JP2009525825A - Fluid delivery system and method - Google Patents

Abstract

The method of dispensing fluid includes three processes. The first of these processes involves pumping fluid into an elastic variable volume dispensing chamber. The dispensing chamber is in series with the normally existing finite fluid impedance and outlet. The impedance is sufficient to cause expansion of the dispensing chamber while receiving the pumped fluid while a portion of the fluid flows through the outlet. Another of these processes involves repeatedly measuring parameters related to the volume of the dispensing chamber over time. The third of these processes involves controlling the pumping of the fluid based on repeated measurement of parameters to produce the desired fluid flow through the outlet. A corresponding system for dispensing fluids implements these processes.

Description

  The present application relates generally to pumping fluid delivery systems and methods that employ a force assembly.

  Many potentially beneficial drugs or compounds, including biologics, are not orally effective due to low absorption rates, hepatic metabolism, or other pharmacokinetic factors. In addition, some therapeutic compounds can be absorbed orally, but sometimes require frequent administration and it is difficult for the patient to maintain the desired schedule. In such cases, parenteral delivery is often or can be employed.

  Effective parenteral routes of drug delivery and other fluids and compounds such as subcutaneous injection, intramuscular injection, and intravenous (IV) administration include puncture of the skin with a needle or stylet. Insulin is an example of a therapeutic fluid that is self-injected by millions of diabetics. Users of drugs delivered parenterally will benefit from wearable devices that automatically deliver the required drug / compound over a period of time.

  In order to achieve this goal, efforts have been made to design portable devices for the controlled release of therapeutic agents. Such devices are known to have a reservoir, such as a cartridge, syringe, or bag, and to be electronically controlled. These devices suffer from a number of drawbacks, including malfunction rates. It is also an ongoing challenge to reduce the size, weight, and cost of these devices.

  In one embodiment, the present invention provides a method of dispensing a fluid. In the present embodiment, the method includes three processes. The first of these processes involves pumping fluid into an elastic variable volume dispensing chamber. The dispensing chamber is in series with the normally existing finite fluid impedance and outlet. The impedance is sufficient to cause expansion of the dispensing chamber while receiving the pumped fluid while a portion of the fluid flows through the outlet. Another of these processes involves repeatedly measuring parameters related to the volume of the dispensing chamber over time. The third of these processes involves controlling the pumping of the fluid based on repeated measurement of parameters to produce the desired fluid flow through the outlet.

In related embodiments, repeatedly measuring the parameter includes acoustically exciting a gas in an acoustically continuous region and producing an acoustic response therein. The region includes a sub-region connected to the dispensing chamber, so that a volume change of the sub-region occurs due to a volume change of the dispensing chamber. The embodiment also includes the step of characterizing the acoustic response.
In a further related embodiment, the step of acoustically exciting the gas is performed at a single frequency only. Also, characterizing the acoustic response includes determining a phase relationship between the acoustic response measured at the first location in the acoustically continuous region and a single frequency reference value. The method of this embodiment further includes calculating a sub-region volume change based on the temporal evolution of the phase relationship.

  Alternatively or additionally, the impedance is a passive impedance. The passive impedance may optionally include a conduit. The conduit may have any of several forms. A coiled tube may be included. The coiled tube may include at least two turning points. Alternatively or additionally, the conduit has a serpentine shape.

  Alternatively or additionally, the conduit has a length and an inner diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid. Optionally, the inner diameter is sufficiently large to prevent occlusion due to the flow of therapeutic agent flowing through the conduit. Optionally, the conduit has a length greater than 2 cm.

  In a further embodiment, the method includes providing an injection line connectable with the upstream fluid source. The injection line is in fluid communication downstream with the pumping chamber. The pumping chamber has a pump outlet. The method also includes activating the force assembly to limit fluid backflow to the inlet while pressurizing the pumping chamber and energizing flow to the pump outlet.

  In a related embodiment, actuating the force assembly includes utilizing the movement of the force assembly between work strokes to limit backflow and pressurize the pumping chamber in a single mechanical action. In a further related embodiment, the backflow is limited by a given mobility of the force actuating assembly and pressurized to the pumping chamber by a greater mobility.

  In a further related embodiment, actuating the force assembly includes limiting back flow to the fluid source by closing the infusion line. Alternatively or additionally, the method also includes the step of preventing reverse flow of fluid from the dispensing chamber to the pumping chamber using a passive valve mounted therebetween.

  In another related embodiment, a portion of the pumped fluid does not enter the dispensing chamber, for example by providing a shunt line back from the pump outlet to the fluid source (e.g., non-added). You may make it return to a pressure fluid reservoir.

  In another related embodiment, the three processes described above are performed by components in a patch-sized housing. The housing has a maximum dimension and the conduit has a length that exceeds the maximum dimension.

  Optionally, the conduit includes a length and an inner diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid. Also optionally, the dispensing chamber has an inlet and the conduit has an inner diameter that is smaller than the inner diameter of the dispensing chamber inlet.

  In another embodiment, the present invention provides an apparatus for dispensing fluid. In this embodiment, the apparatus includes a patch-sized housing, a pump enclosed within the housing, and a pump downstream dispensing assembly in fluid communication with the pump. The dispensing assembly includes an elastic dispensing chamber and a sensor for quantitatively measuring a volume related parameter or a derivative of the volume with respect to time. The pump pulsates fluid pulsatingly to expand the elastic dispensing chamber with each cycle, and the chamber repeatedly delivers fluid to the outlet. The device is also coupled to a sensor and a pump for controlling the operation of the pump during normal flow conditions based on the measured parameters to achieve delivery of a fluid having a desired cumulative volume. A control loop is also included. The loop includes a controller that determines the cumulative volume of fluid delivered through the outlet based on the measured parameters.

  Further related embodiments also include an acoustic energy source that acoustically excites a gas in an acoustically continuous region and produces an acoustic response therein. The region includes a sub-region coupled to the dispensing chamber, thereby causing a volume change of the sub-region due to a volume change of the dispensing chamber. Furthermore, the present embodiment includes a processor, wherein the sensor is a first acoustic transducer mounted at a first position in an acoustically continuous region to generate an electrical signal based on the acoustic response. including. The processor is coupled to the first acoustic transducer and the reference value and implements a flow determination process for determining an amount related to the volume change of the sub-region based on the acoustic response.

  Optionally, the acoustic energy source excites the gas at a single frequency only, the electrical signal generated by the first acoustic transducer has a phase relationship to the reference value, and the flow determination process further Based on temporal evolution, an amount for subregion volume change is determined.

  Optionally, in addition, the apparatus of this embodiment further includes a finite fluid impedance coupled to the outlet. The impedance is sufficient to allow such expansion of the elastic dispensing chamber. Optionally, the impedance is a passive impedance. The passive impedance may optionally include a conduit. For the method described above, the conduit may have any of several forms. A coiled tube may be included. The coiled tube may include at least two turning points. Alternatively or additionally, the conduit has a serpentine shape.

  Alternatively or additionally, the conduit has a length and an inner diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid. Optionally, the inner diameter is sufficiently large to prevent occlusion due to the flow of therapeutic agent flowing through the conduit. Optionally, the conduit has a length greater than 2 cm.

  In a further related embodiment, the housing has a maximum dimension and the conduit has a length that exceeds the maximum dimension. Optionally, the dispensing chamber has an inlet and the conduit has an inner diameter that is smaller than the inner diameter of the dispensing chamber inlet.

  Optionally, the present invention provides a system for pumping fluid through a line. In this embodiment, the system includes a pumping chamber having a connectable inlet for providing fluid communication with a fluid source and a pump outlet. The system also includes a force assembly adapted to provide a compression stroke to the pumping chamber. In this embodiment, the compression stroke limits the back flow of fluid from the pumping chamber to the inlet, while energizing the fluid from the pumping chamber to the pump outlet.

  Optionally, the force assembly is coupled to the inlet valve actuator and the pump actuator so that when the compression stroke is energized by the pump actuator from the pumping chamber to the pump outlet, the inlet and fluid source Actuate the inlet valve connected between and close the valve.

  Optionally, the force assembly includes a plate coupled to the valve actuator, the pump actuator, and a motor for coordinated operation of the valve actuator and the pump actuator. Optionally, the motor includes a shape memory actuator. Also optionally, the motor includes at least one pulley for folding the shape memory actuator and fitting within the reusable part. Optionally, the force assembly includes a motor.

  Additionally or alternatively, a shunt line is provided in fluid communication with the pump outlet and a fluid source (eg, a non-pressurized fluid reservoir) so that a portion of the fluid discharged by the pump is returned to the fluid source. Also good.

  In another embodiment, the present invention provides an apparatus for dispensing fluid, wherein the apparatus includes a patch-sized housing. The enclosure encloses a pressurized fluid source in series with the downstream flow-inhibiting distorted conduit.

  In a further related embodiment, the apparatus further includes a sensor for measuring a parameter related to the fluid flow to the conduit and a control loop for adjusting the fluid flow based on the measured parameter.

  Optionally, the source includes a pump operably coupled to provide pressurized fluid to the downstream flow-inhibiting distorted conduit. Also optionally, the apparatus includes a sensor for measuring a parameter relating to the fluid flow to the conduit and a control loop for adjusting the operation of the pump based on the measured parameter.

  Optionally, the present invention provides a system for pumping fluid through a line. In this embodiment, the system includes a pumping chamber having a connectable inlet for providing fluid communication with a fluid source and a pump outlet. The system also includes a force assembly adapted to provide a compression stroke to the pumping chamber. In this embodiment, the compression stroke limits the back flow of fluid from the pumping chamber to the inlet, while energizing the fluid from the pumping chamber to the pump outlet.

  Optionally, the force assembly is coupled to the inlet valve actuator and the pump actuator so that when the compression stroke is energized by the pump actuator from the pumping chamber to the pump outlet, the inlet and fluid source Actuate the inlet valve connected between and close the valve.

  Optionally, the force assembly includes a plate coupled to the valve actuator, the pump actuator, and a motor for coordinated operation of the valve actuator and the pump actuator. Optionally, the motor includes a shape memory actuator. Also optionally, the motor includes at least one pulley for folding the shape memory actuator and fitting within the reusable part. Optionally, the force assembly includes a motor.

  Additionally or alternatively, a shunt line is provided in fluid communication with the pump outlet and a fluid source (eg, a non-pressurized fluid reservoir) so that a portion of the fluid discharged by the pump is returned to the fluid source. Also good.

  In further related embodiments, the source further includes a non-pressurized reservoir operably coupled to provide fluid to the pump.

  As in the above-described embodiments, the flow-inhibiting distorted conduit may be implemented in various ways. For example, it may be coiled. It may include at least two turning points. Alternatively or additionally, the flow inhibition distorted conduit has a serpentine shape. Optionally, the housing includes a disposable portion having an integral fluid path with a flow-inhibiting distorted conduit. Also optionally, the conduit is disposed within the housing. Optionally, the conduit has a length and an inner diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid. Optionally, the inner diameter is sufficiently large to prevent occlusion due to the flow of therapeutic agent flowing through the conduit. Optionally, the conduit has a length greater than 2 cm. Optionally, the housing has a maximum dimension and the conduit has a length that exceeds the maximum dimension.

  In further related embodiments, the apparatus additionally includes a dispensing chamber in fluid communication with the source and the conduit. The dispensing chamber includes an inlet that receives fluid from the source and an outlet through which fluid is provided to the conduit. Optionally, the conduit has an inner diameter that is smaller than the inner diameter of the dispensing chamber inlet.

  Alternatively or additionally, the dispensing chamber is an elastic variable volume dispensing chamber. Optionally, the conduit has an effective diameter that is smaller than the effective diameter of the inlet.

  Optionally, the present invention provides a system for pumping fluid through a line. In this embodiment, the system includes a pumping chamber having a connectable inlet for providing fluid communication with a fluid source and a pump outlet. The system also includes a force assembly adapted to provide a compression stroke to the pumping chamber. In this embodiment, the compression stroke limits the back flow of fluid from the pumping chamber to the inlet, while energizing the fluid from the pumping chamber to the pump outlet.

  Optionally, the force assembly is coupled to the inlet valve actuator and the pump actuator so that when the compression stroke is energized by the pump actuator from the pumping chamber to the pump outlet, the inlet and fluid source Actuate the inlet valve connected between and close the valve.

  Optionally, the force assembly includes a plate coupled to the valve actuator, the pump actuator, and a motor for coordinated operation of the valve actuator and the pump actuator. Optionally, the motor includes a shape memory actuator. Also optionally, the motor includes at least one pulley for folding the shape memory actuator and fitting within the reusable part. Optionally, the force assembly includes a motor.

  Additionally or alternatively, a shunt line is provided in fluid communication with the pump outlet and a fluid source (eg, a non-pressurized fluid reservoir) so that a portion of the fluid discharged by the pump is returned to the fluid source. Also good.

  In another embodiment, the present invention provides an apparatus for dispensing fluid. The apparatus includes a patch-sized housing and a pump disposed within the housing. The pump has a pump discharge port. A dispensing chamber is also included that is also disposed within the housing. The dispensing chamber has a dispensing inlet and a dispensing outlet. The dispensing inlet is connected to the pump outlet. The apparatus also includes a distorted conduit connected to the dispensing outlet to provide flow impedance.

  Optionally, the apparatus includes a sensor for measuring a parameter related to the fluid flow to the conduit and a control loop for adjusting the fluid flow based on the measured parameter. Optionally, the device further includes a non-pressurized reservoir disposed within the housing and operably coupled to provide fluid to the pump inlet.

  As in the previous embodiment, the distorted conduit may be implemented in various ways. For example, it may be coiled. It may include at least two turning points. Alternatively or additionally, the distorted conduit has a serpentine shape. Optionally, the conduit is disposed with the housing. Optionally, the housing includes a disposable portion having an integral fluid path with a distorted conduit. Optionally, the conduit has a length greater than 2 cm. Optionally, the housing has a maximum dimension and the conduit has a length that exceeds the maximum dimension. Optionally, the conduit has a length and an inner diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid. Optionally, the conduit has a length and an inner diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid. Optionally, the inner diameter is sufficiently large to prevent occlusion due to the flow of therapeutic agent flowing through the conduit.

  Optionally, the dispensing chamber is an elastic variable volume dispensing chamber. Also optionally, the dispensing chamber has an inlet and the conduit has an inner diameter that is smaller than the inner diameter of the dispensing chamber inlet.

  In another embodiment, the present invention provides a method for measuring fluid flow delivered through a line. The method of this embodiment provides for the gas in an acoustically continuous region only at a single frequency during the volume change of the acoustically continuous region caused by fluid flow in a zone coupled to the volume of the subregion. Is acoustically excited to produce an acoustic response. Further, the method is based on determining a phase relationship between the acoustic response measured at a first location in the acoustically continuous region and a single frequency reference value, and temporal evolution of the phase relationship. And calculating a change in the volume of the sub-region and inferring a measured value of the fluid flow rate through the line based on the volume change of the gas in the sub-region.

  Optionally, the method further comprises measuring a reference value at a second position in the acoustically continuous region. Also optionally, the zone is connected to the volume of the sub-region via a membrane.

  In a further related embodiment, acoustically exciting the gas includes driving a transducer. Optionally, acoustically exciting the gas includes driving a speaker. This embodiment optionally includes calibrating the phase relationship as a function of sub-region volume. Optionally, the acoustically continuous region has a volume of less than 200 microliters. In a further embodiment, the acoustically continuous region has a volume of less than 130 microliters. In another further embodiment, the acoustically continuous region has a volume of less than 10 microliters.

  Optionally, calculating the volume change includes determining such change having a resolution better than 20 nanoliters. In a further embodiment, calculating the volume change includes determining such change having a resolution better than 15 nanoliters. In a further embodiment, calculating the volume change includes determining such a change having a resolution better than 13 nanoliters. In another further embodiment, calculating the volume change comprises determining such a change having a resolution of at least 1/10000 of the volume of the acoustically continuous region.

  Optionally, the single frequency is at or near the sub-region resonance frequency.

  In a further related embodiment, the method performs a calibration step by acoustically exciting the region at a series of frequencies, and measuring an acoustic response at a first location in the acoustically continuous region; The method further includes determining a transfer function characterizing the phase relationship of each of the series of frequencies as a function of frequency with a respective reference value.

  Optionally, the method further comprises measuring a respective reference value for the series of frequencies at a second location in the acoustically continuous region. Alternatively or additionally, the method further comprises detecting the presence of bubbles based on the transfer function. Optionally, the method further includes entering an alarm condition based on detecting the presence of bubbles. Optionally, the step of calculating the volume change is repeated during the measurement phase, the measurement phase alternating with the calibration phase. In a further related embodiment, the fluid is delivered every cycle and the calibration and measurement phase is coordinated with the cycle.

  In another embodiment, the present invention provides a system for measuring fluid flow delivered through a line. In this embodiment, the system is in an acoustically continuous region only at a single frequency during a volume change of the acoustically continuous region caused by fluid flow in a zone coupled to the volume of the subregion. An acoustic energy source for acoustically exciting the gas and producing an acoustic response is included. The system also includes a first acoustic transducer mounted at a first location in an acoustically continuous region to generate an electrical signal based on the acoustic response. The electrical signal of the first acoustic transducer has a phase relationship with respect to the reference value. The system is also coupled to the first acoustic transducer and the reference value, determines an amount related to the volume change of the sub-region based on the temporal evolution of the phase relationship, and based on the volume change of the gas in the sub-region. And a processor that implements a flow determination process for inferring a measurement of the fluid flow through the line.

  Optionally, the system further includes a second acoustic transducer for generating an electrical signal that is mounted at a second location in an acoustically continuous region and that constitutes a reference value. Also optionally, the system has a power consumption of less than 500 joules per day.

  In a further related embodiment, a fluid delivery system is provided that utilizes a system that measures fluid flow delivered through a line in accordance with the embodiments described above. The fluid delivery system of this embodiment creates a flow of fluid delivered through the line and additionally includes a pump coupled to the processor.

  Optionally, the present invention provides a system for pumping fluid through a line. In this embodiment, the system includes a pumping chamber having a connectable inlet for providing fluid communication with a fluid source and a pump outlet. The system also includes a force assembly adapted to provide a compression stroke to the pumping chamber. In this embodiment, the compression stroke limits the back flow of fluid from the pumping chamber to the inlet, while energizing the fluid from the pumping chamber to the pump outlet.

  Optionally, the force assembly is coupled to the inlet valve actuator and the pump actuator so that when the compression stroke is energized by the pump actuator from the pumping chamber to the pump outlet, the inlet and fluid source Actuate the inlet valve connected between and close the valve.

  Optionally, the force assembly includes a plate coupled to the valve actuator, the pump actuator, and a motor for coordinated operation of the valve actuator and the pump actuator. Optionally, the motor includes a shape memory actuator. Also optionally, the motor includes at least one pulley for folding the shape memory actuator and fitting within the reusable part. Optionally, the force assembly includes a motor.

  The power consumption by the processor does not substantially exceed the power consumption by the pump. Optionally, the system further comprises a membrane connecting the zone to the subregion volume. Also optionally, the acoustic energy source includes an acoustic transducer coupled to the electrical signal. Optionally, the transducer is a speaker.

  In a further related embodiment, the processor implements a calibration process for calibrating the phase relationship as a function of sub-region volume. Optionally, the acoustically continuous region has a volume of less than 200 microliters. In a further embodiment, the acoustically continuous region has a volume of less than 130 microliters. In another further embodiment, the acoustically continuous region has a volume of less than 10 microliters.

  Alternatively or additionally, the flow determination process determines an amount related to the volume change that corresponds to a resolution better than 20 nanoliters. In a further embodiment, the flow determination process determines an amount for volume change that corresponds to a resolution better than 15 nanoliters. In a further embodiment, the flow determination process determines an amount related to the volume change that corresponds to a resolution better than 13 nanoliters. In another further embodiment, the flow determination process determines an amount related to volume change that corresponds to a resolution of at least 1/10000 of the volume of the acoustically continuous region.

  Optionally, the single frequency is at or near the sub-region resonance frequency. In a further embodiment, the acoustic source includes an acoustic radiation transducer coupled to the processor. In addition, the processor implements a calibration process that causes the acoustic source to acoustically excite the region at a series of frequencies, and as part of such a process, the processor includes an electrical signal of the first transducer and a function of frequency. A transfer function that characterizes the phase relationship between each of the series of frequencies and the reference value is determined.

  In a further embodiment, the processor implements a bubble detection process for detecting the presence of bubbles based on the transfer function. Optionally, the bubble detection process causes the system to enter an alarm state based on detecting the presence of bubbles.

  In a further embodiment, the flow determination process is repeated during the measurement phase, and the measurement phase alternates with the calibration phase. Optionally, fluid is delivered every cycle, and the calibration and measurement phase is coordinated with the cycle.

  These aspects of the invention are not meant to be exclusive, and other features, aspects, and advantages of the present invention will become more apparent when read in conjunction with the appended claims and accompanying drawings. It will be readily apparent to those skilled in the art.

  It should be noted that the elements depicted in the accompanying drawings and the description are not necessarily drawn to scale or to any scale.

(Definition)
As used in this description and the appended claims, the following terms shall have the indicated meanings unless the context requires otherwise.

  The “user input” of the device includes any mechanism by which the user or other operator of the device can control the functions of the device. User inputs include mechanical arrays (eg, switches, push buttons), communication wireless interfaces with remote controls (eg, RF, infrared), acoustic interfaces (eg, with voice recognition), computer networks, Interfaces (eg, USB ports), and other types of interfaces may be included.

  A “button” in the context of a user input, such as the so-called “Bolus button” discussed below, can be any type of user input capable of performing a desired function and is limited to a push button. Not.

  An “alarm” includes any mechanism that can generate a warning to a user or a third party. Alarms can be audible alarms (eg, speakers, buzzers, sound generators), visual alarms (eg, LEDs, LCD screens), tactile alarms (eg, vibration elements), wireless signals (eg, remote control devices or caregivers) Wireless transmission), or other mechanisms. Alarms include redundant mechanisms (eg, two different audible alarms) or complementary mechanisms (eg, audible alarms, tactile alarms, and wireless alarms), using multiple mechanisms simultaneously, in parallel, or in sequence. May be generated.

  “Fluid” means, for example, a substance such as a liquid that can flow through a flow line.

  “Impedance” shall mean the resistance of a device or flow line to the flow of fluid flowing therethrough.

  “Wetted surface” describes a component that is in direct contact with the fluid during normal fluid delivery operations. Since fluids are not limited to liquids, “wetted” components are not necessarily wetted.

  A “patient” includes a person or animal that receives fluid from a fluid delivery device, whether part of treatment or otherwise.

  “Cannula” shall mean a disposable device capable of injecting fluid into a patient. A cannula as used herein may represent a conventional cannula or needle.

  “Analyte sensor” shall mean any sensor capable of determining the presence of an analyte in a patient. Analyte sensor embodiments include, but are not limited to, sensors capable of determining the presence of any viral, parasitic, bacterial, or chemical analyte. The term “analyte” includes glucose. The analyte sensor may communicate with other components in the fluid delivery device (eg, a control device in a non-disposable part) and / or a remote control device.

  “Dispensing assembly sensor” shall mean a mechanism for determining the volume of fluid present in a dispensing chamber.

  "Sharp" shall mean anything that can be pierced or projected into animal skin, in particular human skin. The sharp portion may include a cannula, a cannula insertion device, an analyte sensor, or an analyte sensor insertion device. The sharps may be provided separately or may be provided together, eg, in a cartridge.

  “Disposable” refers to a part, device, part, or the like that is used during a fixed period of time and is then intended to be discarded and replaced.

  “Non-disposable” refers to a reusable part intended to have an indefinite period of use.

  “Patch size” is a size that is small enough to be fixed so that it is fixed to a patient's skin and attached as a medical device, such as by an adhesive or strap, during administration of a substance contained within the device It means that. Medical devices that are small enough to function as an implant are within the scope of this definition.

  “Normally present finite fluid impedance” shall mean a finite fluid impedance that exists in a given process of fluid delivery, ie, when there is no fault condition (eg, occlusion).

  A “passive” impedance is one that is not actively controlled during the pumping cycle.

  “Acoustic volume measurement” refers to an associated volume using acoustic techniques such as those described in US Pat. Nos. 5,349,852 and 5,641,892 and the techniques described herein. It shall mean the quantitative measurement of

  A “temperature sensor” includes any mechanism for measuring temperature and communicating temperature information to a controller. The apparatus may include one or more temperature sensors for measuring skin temperature, AVS temperature, ambient temperature, fluid temperature, and the like.

  Embodiments of the devices, pumping mechanisms, systems, and methods described herein relate to fluid delivery, including fluid pumping and volumetric measurements, and their actuation and control. Device embodiments include portable or non-portable devices for fluid delivery. Some embodiments of the device include a disposable base and a non-disposable top. The device includes embodiments in which the infusion device is inserted directly into the patient through the base. These device embodiments are patch pump devices. The patch pump may be adhered to the patient using an adhesive, strap, or other suitable arrangement. The adhesive may have protective peelable strips that can be removed prior to use to expose the adhesive.

  However, in other embodiments, the fluid delivery device is a portable device where the tube is connected to the fluid line. The tube is typically connected to the patient through a cannula.

  In some embodiments where a disposable base and a non-disposable top are implemented, the base includes a wetted part, and the part included in the non-disposable top is typically a non-wetted part. It is.

  Various embodiments of the pumping mechanism include an upstream inlet valve, a pumping actuating member, a downstream outlet valve, and a movable member. In some embodiments, the pumping actuation member and the downstream valve function are implemented using the same device. The pumping mechanism pumps fluid from the reservoir through the fluid line to the outlet. Pumping mechanisms are typically employed with non-pressurized reservoirs, however, the scope of the present invention is not so limited.

  In one embodiment of the fluid delivery system, the device includes an analyte sensor housing. The analyte sensor is introduced into the patient through the analyte sensor housing at the base of the device. In these embodiments, the infusion device is also introduced through a cannula housing on the base of the device. In these embodiments, the device is worn by the user as a patch pump.

  The system typically includes a controller that may include a wireless transceiver. Thus, the device may be controlled exclusively or partially through the radio controller. The control device may receive information from the analyte sensor and / or fluid delivery device via wireless communication. A patient or a third party can use the control device to control the function of the fluid delivery device.

  In one embodiment of the fluid delivery device, the device is an insulin pump and the analyte sensor is a blood glucose sensor. A controller that receives information related to both the volume of insulin delivered (or the number of pump strokes over time) and the blood glucose data assists the user in programming the operating schedule for the pump mechanism. .

  Exemplary dispensing assemblies and volume sensing devices are described herein. The dispensing assembly includes at least one microphone and a loudspeaker. The assembly measures the volume change in the dispensing chamber and determines the fluid volume to be pumped. Volume sensing data is used to determine the state of the fluid delivery device. Thus, the various controls may rely on volume sensing data.

  In an embodiment of the present invention, the user configures the fluid delivery device via the user interface to cause the fluid delivery device to deliver fluid in an appropriate manner. In one embodiment, the user interface resides on a separate portable user interface assembly that can be in wireless communication with the patch. The patch may be disposable or partially disposable.

  An exemplary use of embodiments of the device is the delivery of insulin to a diabetic patient, but as mentioned above, other uses include the delivery of any fluid. The fluid includes analgesics for painful individuals, chemotherapeutic agents for cancer patients, and enzymes for patients with metabolic diseases. Various therapeutic fluids may include small molecules, natural products, peptides, proteins, nucleic acids, carbohydrates, nanoparticle suspensions, and related pharmaceutically acceptable carrier molecules. A therapeutically effective molecule may be modified to improve stability within the delivery device (eg, by pegylation of a peptide or protein). Although illustrative embodiments herein describe drug delivery applications, the embodiments include liquid dispensing of reagents for high-throughput analytical measurements such as lab-on-chip applications and capillary chromatography. It may be used for other applications. For purposes of the following description, the terms “therapeutic agent” or “fluid” are used interchangeably, however, as described above, any fluid can be used in other embodiments. Thus, the devices and descriptions contained herein are not limited to the use of therapeutic agents.

  An exemplary embodiment includes a reservoir for holding a supply of fluid. In the case of insulin, the reservoir may be conveniently sized to hold enough insulin for delivery for one or more days. For example, the reservoir may hold about 1-2 ml of insulin. A 2 ml insulin reservoir may correspond to a supply of about 3 days for about 90% of potential users. In other embodiments, the reservoir can be of any size or shape and can be adapted to hold any amount of insulin or other fluid. In some embodiments, the size and shape of the reservoir is related to the type of fluid that the reservoir is adapted to hold. The fluid reservoir may be eccentrically or irregularly shaped and / or may be wedged to prevent improper installation or use.

  Some fluid delivery device embodiments are adapted for use by diabetic patients and, therefore, in these embodiments, the device delivers insulin that complements or replaces the action of the patient's islet beta cells. Embodiments adapted for insulin delivery seek to mimic the action of the pancreas by providing both a basal level of fluid delivery as well as a bolus level of delivery. Basal level, bolus level, and timing can be set by the patient or another party by using a wireless handheld user interface. Further, basal and / or bolus levels can be triggered or adjusted in response to the output of an integrated or external analyte sensor such as a glucose monitoring device or a blood glucose sensor. In some embodiments, the bolus can be triggered by the patient or a third party using a designated button or other input means located on the fluid delivery device. In yet other embodiments, the bolus or foundation can be programmed or managed through a user interface located on the fluid delivery device.

  FIG. 1 illustrates a patient 12 wearing a fluid delivery device 10 and holding a wireless user interface assembly 14 for monitoring and adjusting the operation of the fluid delivery device 10 in accordance with an exemplary embodiment of the present invention. The user interface assembly 14 typically includes an instrument for entering information (such as a touch screen or keypad) and an instrument for transmitting information to the user (such as an LCD display, speaker, or vibration alarm). Including. The fluid delivery device is typically small and lightweight enough to remain comfortably adhered to the patient for several days.

  The fluid delivery device 10 is shown worn on the arm of a patient 12 in FIG. In other embodiments, the fluid delivery device 10 may be mounted at other locations in the patient where the particular fluid to be delivered can be advantageously utilized by the patient's body. For example, the fluid may be advantageously delivered to the patient's abdomen, kidney region, lower limbs, or otherwise.

  Referring now to FIG. 2A, a schematic diagram of the fluid delivery device 10 having a feedback loop 360 from the dispensing assembly 120 to the pumping assembly 16 is shown. Pumping assembly 16 pumps fluid to dispensing assembly 120. The fluid then flows out to an outlet assembly 17 that includes a flow restrictor 340 and an output. The output typically includes a cannula and leads to the patient. The dispensing assembly 120 may include an elastic variable volume dispensing chamber, at least one microphone, and a loudspeaker for measuring parameters related to the flow rate through the output over time. Feedback loop 360 allows for adjustment of the operation of pumping assembly 16 based on repeated measurements made by the sensor. The flow restrictor 340 creates a high impedance between the dispensing assembly 120 and the output of the flow line 5010. The flow restrictor 340 can be, for example, a small diameter tube or a section of a microtubule. Referring now to FIG. 2B, in one embodiment, the pumping assembly 16 pumps fluid from the reservoir 20 to the dispensing assembly 120.

  Referring now to FIG. 3, a block diagram of a further embodiment that employs fluid principles is shown. The flow line 310 connects the reservoir 20, the pumping assembly 16, the dispensing assembly 120, and the outlet assembly 17. The outlet assembly 17 may include a high impedance flow restrictor 340 and an infusion device 5010 (eg, a cannula). The output of the flow restrictor 340 is sent to the infusion device 5010 for delivery to the patient. The flow restrictor 340 has a higher flow impedance than a portion of the flow line 310 upstream of the dispensing assembly 120. Thus, the pumping assembly 16 can pump fluid to the dispensing assembly 120 faster than the fluid that can flow out of the outlet assembly 17. The dispensing assembly 120 may include a variable volume dispensing chamber 122 having an elastic wall. In the embodiments presented below, the elastic wall is a membrane. Examples of membrane materials include silicones, nitriles, and any other materials that have the desired elasticity and properties to function as described herein. In addition, other structures can serve the same purpose. As a result of the action of the pumping assembly 16, it receives a constant fluid loading, and the elasticity of the membrane first expands the chamber 122 and then passes the fluid content of the dispensing assembly 120 from the flow restrictor 340 to the patient. It is possible to provide the delivery pressure necessary to achieve this. When an appropriate sensor (an example is described below) is placed, the dispensing assembly 120 may measure the flow rate of fluid flowing through the variable volume dispensing chamber 122 and further provide feedback through the feedback loop 360. Provided, the pumping assembly 16 may control the timing and / or rate at which the dispensing chamber 122 is pumped or partially filled, thereby delivering the desired dose to the patient at the desired rate.

  Referring again to FIG. 3, the flow restrictor 340 further prevents fluid flow exceeding a specified flow rate. Furthermore, since pressurized fluid delivery is achieved through the interaction of pumping assembly 16, dispensing assembly 120, and flow restrictor 340, non-pressurized reservoir 20 can be employed.

Still referring to FIG. 3, the feedback loop 360 may include a controller 501. The controller 501 may include a processor and control circuitry for operating the pumping assembly 16 and pumping fluid to the dispensing assembly 120. The controller 501 repeatedly receives parameters relating to fluid flow from the sensor, which may be integral with the dispensing assembly 120, and uses this parameter to control the pumping assembly 16 to control the desired flow through the output. Achieve. For example, the controller 501 can adjust the timing or operating range of the pumping assembly 16 to achieve a desired basal or bolus flow rate and / or deliver a desired basal or bolus accumulation dose. In determining the timing or range of pumping, controller 501 uses the output of a sensor (not shown) to estimate (among other things) fluid flow rate, accumulated fluid flow rate, or both, and then based on the estimate An appropriate compensation action may be determined. In various embodiments, pumping can occur with pulses that can be delivered between 10 ⁻⁹ liters per pulse to microliters per pulse. Steady or bolus doses may be achieved by delivering multiple pulses (examples of basal and bolus doses are presented and described below).

  The use of a partially collapsible non-pressurized reservoir 20 can advantageously prevent air accumulation in the reservoir as the fluid in the reservoir is depleted. The reservoir 20 may be connected to the fluid line 310 through a diaphragm (not shown). In particular, when the system is tilted such that a hollow area is interposed between the fluid contained in the reservoir and the diaphragm of the reservoir 20, the air accumulation in the vented reservoir causes fluid release from the reservoir 20. It can be prevented. The tilt of the system is expected during normal operation as a wearable device. 104-106C depict views of various embodiments and one embodiment of a reservoir. Further description of the reservoir is also included below.

  4A-4C, various embodiments of the flow restrictor 340 are shown. Referring now to FIG. 4A, the flow restrictor is a molded flow channel 340 and may be a molded groove (not shown) in the base. In one embodiment, the cross section of the shaped flow channel 340 is about 0.009 inches. In this embodiment, the flow restrictor 340 is formed into a tool. Referring now to FIG. 4B, a microtubule 340 is shown as an alternative embodiment flow restrictor. In one embodiment, the microtubule has an inner diameter of about 0.009 inches. Both shaped flow channels and microtubules use a long path with a small inner diameter or cross section to provide flow impedance. Next, referring to FIG. 4C, the precision hole is shown as a flow restrictor 340. In one embodiment, the precision hole is a plate with a laser drill hole. In alternative embodiments, any flow impedance device or method known in the art can be used.

  In general, in contrast to prior art fluid delivery systems having an active downstream valve that can be considered to produce an infinite fluid impedance in a functional sense, the flow restrictor 340 generates a finite fluid impedance. Also, in contrast to prior art systems, impedance is usually also present from time to time, rather than being able to be disturbed by an occlusion. As a result of the finite nature of the fluid impedance, in embodiments including the dispensing chamber 122, fluid can leak out of the outlet while the dispensing chamber 122 is expanding.

  5-8 schematically illustrate cross-sectional views of an exemplary embodiment of dispensing assembly 120. It should be understood that the delivery of fluids for other purposes, such as industrial processes, is within the scope of the present invention, and that certain terminology is only an example. As shown in FIG. 5, the dispensing assembly 120 may include a variable volume dispensing chamber 122 and a sensor 550. The variable volume dispensing chamber 122 includes an elastic dispensing diaphragm 125 that expands and contracts the chamber 122 in response to the flow rate of fluid flowing into and out of the dispensing assembly 120. In certain embodiments of the invention, the variable volume dispensing chamber 122 may be removable from other elements of the dispensing assembly 120, as further described herein. The concept of an elastic dispensing diaphragm 125 that expands and contracts the chamber 122 is illustrated by a double-headed arrow. The measurement chamber 122 is considered to include a portion of the line 110 that is characterized by fluid flow, designated by arrows 112 in FIG. Neither the fluid flow 112 or the end position or nature of the line 110 need to limit the scope of the invention as claimed in the specific claims attached hereto. The flow restrictor 340 causes fluid to drain out of the dispensing chamber 122 more slowly when fluid is pumped into the chamber 122 by the pumping assembly 16 than fluid flows into the chamber 122. As a result, the dispensing chamber 122 expands and pressurizes when a constant fluid charge flows in. Dispensing diaphragm 125, which is deformed by expansion of dispensing chamber 122, provides the force required to deliver the measured volume through flow restrictor 340 to outlet assembly 17. As described above, the sensor 550 repeatedly measures a parameter, such as displacement, or a thermodynamic variable or capacitance that may be related to the volume of the elastic dispensing chamber 122. Using the volumetric measurement generated by sensor 550, the pumping assembly pumps fluid into dispensing chamber 122 so that the proper flow rate of fluid is transferred to and from outlet assembly 17 and subsequent lines, for example, The timing and speed delivered to the patient may be controlled through a feedback loop. The sensor 550 employs, for example, an acoustic volume sensor (detailed below), or other methods (in other embodiments, optical, or capacitance) to determine volume or volume related parameters. May be. Acoustic volumetric techniques are described in US Pat. Nos. 5,575,310 and 5,755,683 by DEKA Products Limited Partnership, and co-pending provisional US patent application 60/60, filed April 5, 2006. 789,243, “METHOD OF VOLUME MEASUREMENT FOR FLOW CONTROL” (all incorporated herein by reference). A fluid volume sensor in the nanoliter range is possible with this embodiment and thus contributes to highly accurate and precise monitoring and delivery. Other alternative techniques for measuring fluid flow may also be used. For example, Doppler method, use of Hall effect sensors in combination with vanes or flapper valves, use of double beams (eg related to flexible members on fluid chambers for sensing distortion of flexible members) ), Use of capacitive sensors with plates, or thermal time-of-flight.

  Referring now to FIGS. 6-9, an embodiment utilizing acoustic volume sensing (AVS) technology as a sensor is shown. The first discussion refers to the embodiment depicted in FIGS. Dispensing assembly 120 has a sensor. It includes a reference chamber 127 and a variable volume measuring chamber 121 connected to a fixed volume chamber 129 by a port 128. Although the present invention may be practiced with reference chamber 127, as shown in FIGS. 6 and 7, in certain other embodiments of the present invention, no reference volume is provided. The volume 129 is referred to herein as “fixed” in terms of terminology, but the real volume at the time scale of acoustic excitation, as in the case where the region referred to as fixed volume 129 is driven by a speaker diaphragm. It should be understood that can vary slightly. The fluid flows from the pumping assembly 16 to the inlet 123 through the elastic dispensing chamber 122 and out of the outlet channel 124. As fluid flows into dispense chamber 122 due to high downstream impedance, dispense diaphragm 125 expands to variable volume chamber 121. An electronic assembly that can be arranged on the printed circuit board 126 includes a loudspeaker 1202, a sensing microphone 1203, and a gas (typically its volume is defined by the position of the dispensing diaphragm 125) (typically And a reference microphone 1201 for measuring acoustic parameters related to air). Sound waves induced by the loudspeaker 134 travel from the fixed volume chamber 129 to the variable volume chamber 121 via the port 128. In addition, the sound wave moves to the reference chamber 127. As the dispensing diaphragm 125 moves with the flow of fluid through the flow line, the volume of air in the variable volume chamber 121 changes, causing a related change in its acoustic properties (which can be detected by a loudspeaker and microphone 1203). . For the same acoustic simulation, the reference microphone 1201 may detect the acoustic characteristics of the fixed reference volume 127. These reference measurements may be used to remove inaccuracies and prevent common mode inaccuracies, for example, in acoustic simulations and other errors. The displacement volume of the fluid may be determined by comparing the measured volume of the variable volume chamber 121 with the initial volume of the variable volume chamber 121. Since the total volume of the dispensing chamber 122 and the variable volume chamber 121 is constant, the absolute volume of the dispensing chamber 122 can also be estimated.

  The embodiment shown in FIG. 6 utilizes an essentially elastic dispensing diaphragm 125, and the embodiment shown in FIG. 7 increases the elasticity of the dispensing chamber 122 when combined with the dispensing diaphragm 125. 5, utilizes an elastic dispensing spring 130 that may allow the use of a flexible (ie less elastic) dispensing diaphragm 125 than is required in the embodiment shown in FIG. The dispense spring 130 is typically positioned adjacent to the dispense diaphragm 125 on the side of the diaphragm 125 that faces the dispense chamber 122.

  Alternatively, loudspeaker 1202 and sensing microphone 1203 may be coupled to variable volume chamber 121 via separate ports to reduce background noise from the microphone. As schematically shown in FIG. 8, the loudspeaker 1202 generates a pressure wave in a fixed loudspeaker volume 6000 that is acoustically coupled to the variable volume chamber 121 via the loudspeaker port 6020. Before being recorded by the sensing microphone 1203, the pressure wave travels from the loudspeaker 1202 through the loudspeaker port 6020 to the variable volume chamber 121 and then to the microphone port 6010. The loudspeaker port 6020 may include a tube portion 6040 with an overhanging opening 6030. Overhang opening 6030 serves to create a uniform length, and the sound wave travels along the entire axis of tube portion 6040 along it. For example, the tube portion 6040 can have a cylindrical shape such as a right circular cylinder or a right circular cylinder. A similar overhang opening may be joined to the tube portion to define the microphone port 6010. In contrast to the AVS sensor of FIGS. 6 and 7, in the embodiment of FIG. 8, the force wave traveling from the loudspeaker 1202 does not have a direct path to the sensing microphone 1203. Thus, the pressure wave from the loudspeaker 1202 is prevented from directly affecting the sensing microphone 1203 without first passing through the variable volume chamber 121. Thus, a low background signal is received by the microphone and an excellent signal to noise ratio is achieved. Further, an upper shelf 6050 may be included in any of the embodiments of FIGS. 6-8 to advantageously reduce the volume of the reference chamber 127.

  In further described embodiments, it may be convenient to make the dispensing chamber removable and disposable by separating the sensor and the measurement chamber portion of the dispensing assembly. In this case, the dispensing chamber is in the disposable section of the patch and the sensor is in the reusable section. The dispensing chamber may be driven by an elastofluid dispensing diaphragm (as shown as 122 and 124 in FIG. 6). Alternatively, as in FIG. 7, the dispensing chamber 122 may be driven by a flexible diaphragm 125. In this case, it is possible to impart elasticity to the dispensing chamber 122 using the dispensing spring 130. When the sensor 550 and the dispensing chamber 122 are joined, the dispensing spring 130 covers the flexible dispensing diaphragm 125. Dispensing spring 130 and dispensing diaphragm 125 may alternatively be employed as a single piece that defines dispensing chamber 122.

  As shown in FIG. 9, an alternative embodiment of a dispensing assembly is shown. In the embodiment of the dispensing assembly 120 depicted in FIG. 9, the variable volume measuring chamber 121 shares a flexible wall (shown here as a flexible diaphragm 125) with the dispensing chamber 122. Port 128 acoustically couples measurement chamber 121 to fixed volume chamber 129 and forms an acoustically continuous region generally designated by numeral 1290. A compressible fluid (typically air or another gas) fills an acoustically continuous region 1290 and is excited by a drive member 1214 (which is itself driven by an actuator 1216). The drive member 1214 may be a speaker diaphragm, such as a hearing aid speaker, and the actuator 1216 is, for example, a voice coil solenoid or a piezoelectric element. Within the scope of the present invention, drive member 1214 may also be coextensive with actuator 1216, for example, drive member 1214 itself may be a piezoelectric element. The drive member 1214 may be included in a drive module 1212 that may contain a reference volume 1220 on the drive member 1214 side distal to the fixed volume 129. However, the reference volume 1220 is typically not employed in the practice of the present invention.

  The reference microphone 1208 is shown in acoustic communication with the fixed volume 129 and the signal microphone 1209 is acoustically coupled to the measurement chamber 121. The volume of the measurement region 121 is provided by one or more microphones 1208, 1209 based on pressure fluctuations (or equivalently acoustic signals) measured at respective positions within the acoustically continuous region 1290. May be determined from the electronic signal. The phase measurement may be performed by comparing the response phase in one or more microphones to the phase of the acoustic excitation or to the response phase at another microphone position. Measurement region 121, and implicitly, the volume of dispensing chamber 122 is based on phase and / or amplitude measurements, as discussed below, from processor 1210 (typically from power supply 1211, shown as a battery. Power is used as the driving force).

  For the purpose of precision delivery of trace amounts of therapeutic agents, delivery of a small but very accurate metered amount per pump stroke is desirable. However, if a small amount of fluid is pumped through line 110 during each pump stroke, very high resolution is required for the measurement process. As a result, according to an embodiment of the invention, the volume change is measured by a sensor 550 having a resolution of at least 10 nanoliters. Measurement of an empty volume with a resolution of 0.01% in the measurement region 121 may be achieved in some embodiments of the invention. According to other embodiments of the invention, sensor 550 provides a resolution greater than 13 nanoliters. In still other embodiments, sensor 550 provides a resolution greater than 15 nanoliters, and in further embodiments, a resolution greater than 20 nanoliters is provided. In such cases, the total volume of the acoustically continuous region 1290 may be less than 130 μl, and in yet other embodiments less than 10 μl.

According to various embodiments of the present invention, based on the filling of the dispensing chamber with a pumped fluid volume flowing through the inlet 123, the dispensing chamber 122, resulting in the variable volume chamber 121 (herein, An a priori model of volume response (also referred to as “measured volume”) may be used. While other models are within the scope of the present invention, one of the models that can be employed depends on the basic volume V _B and the peak displacement V _D depending on the inflow of the pumped fluid and the output of the fixed flow impedance. By representing the fluid volume in dispense chamber 122 as a sum of the exponentially decaying volume that is characterized, the measurement chamber volume during the measurement is characterized as a function of time t as follows: .

一連の音響式測定に対しモデル化された指数関数的減衰（または他の関数モデル）のパラメタリゼーションに適合するために、図６から９に描写されるようなシステムの応答は、以下のように展開される。応答をモデル化する目的のため、ポート１２８は、長さｌおよび直径ｄによって特徴付けられる。理想的な断熱気体の圧力および容積は、ＰＶ^γ＝Ｋによって関連付けられることが可能であり、ここで、Ｋは、本システムの初期状態によって定義される定数である。

In order to fit the parameterization of the exponential decay (or other functional model) modeled for a series of acoustic measurements, the response of the system as depicted in FIGS. 6-9 evolves as follows: Is done. For the purpose of modeling the response, the port 128 is characterized by a length l and a diameter d. The ideal adiabatic gas pressure and volume can be related by PV ^γ = K, where K is a constant defined by the initial state of the system.

  The ideal gas law can be expressed as follows, using a small time-dependent perturbation v (t) in addition to the mean pressure P and volume V, and also the pressure p (t).

本式を微分すると、次のように求められる。

When this equation is differentiated, it is obtained as follows.

音圧レベルが、周囲圧力よりも非常に低い場合、本式は、さらに次のように簡約され得る。

If the sound pressure level is much lower than the ambient pressure, the equation can be further reduced as follows:

圧力に対し理想気体の法則Ｐ＝ｐＲＴを適用および代入すると、次のように求められる。

Applying and substituting the ideal gas law P = pRT for pressure gives:

これは、音速

This is the speed of sound

を用いて、次のように表され得る。

Can be expressed as follows:

また、容積に対する音響式インピーダンスは、次のように定義される。

Moreover, the acoustic impedance with respect to the volume is defined as follows.

一式のモデルによると、音響式ポートは、ポート内の流体はすべて、本質的に、軸方向に往復運動する剛性円柱に応じて移動すると仮定し、モデル化される。チャネル（ポート１２８）内の流体はすべて、同一速度で移動すると仮定され、チャネルは、一定断面であると仮定され、チャネルに流入し、チャネルから流出する流体から生じる「終端効果」は、無視される。

According to a set of models, an acoustic port is modeled assuming that all fluid in the port essentially moves in response to a rigid cylinder reciprocating in the axial direction. All fluids in the channel (port 128) are assumed to move at the same speed, the channel is assumed to have a constant cross-section, and the “termination effect” resulting from fluid flowing into and out of the channel is ignored. The

  This type of laminar friction

と仮定すると、チャネル内の流体の質量に作用する摩擦力は、次のように表され得る：

Assuming that the frictional force acting on the mass of fluid in the channel can be expressed as:

次いで、チャネル内の流体力学に対し、次のように二階微分方程式が表され得る。

A second order differential equation can then be expressed for the fluid dynamics in the channel as follows:

または、容積流量率を用いて、次のように求められる。

Or it calculates | requires as follows using a volumetric flow rate.

次いで、次のようにチャネルの音響式インピーダンスが表され得る。

The acoustic impedance of the channel can then be expressed as follows:

上記で定義された容積およびポート力学を使用して、音響式容積センサシステムが、以下の連立方程式によって表され得る（指数ｋは、スピーカを示し、ｒは、共振器を示す）。

Using the volume and port dynamics defined above, an acoustic volume sensor system can be represented by the following simultaneous equations (the index k indicates a speaker and r indicates a resonator).

同一慣例に従って、

According to the same convention,

とすると、次のように求められる。

Then, it is calculated as follows.

さらに、

further,

とすると、次のように求められる。

Then, it is calculated as follows.

ｐ_２がｐ_１よりも大きい場合、容積は、正方向に加速する傾向にある。

If p ₂ is greater than p _1, volume tends to accelerate in the forward direction.

式数を削減し（ｐ_０を入力として処理）、

Reduce the number of expressions (process with p ₀ as input),

を代入すると、次のように求められる。

Substituting is obtained as follows.

これらの式を使用して、１つの単純表現式が求められる。

Using these equations, one simple expression is obtained.

また、これらの式は、伝達関数形式で表され得る。「スピーカ間」伝達関数ｐ_１／ｐ_０は、次のように求められる。

These equations can also be expressed in transfer function form. The “between speakers” transfer function p ₁ / p ₀ is determined as follows.

または、

Or

ここで、

here,

である。

It is.

Similarly, an “intersystem” transfer function p ₂ / p ₀ based on measurements on one side of port 128 is determined by the following equation:

（システム間位相を使用した容積推定）
同様に、同一原理を使用して、伝達関数が容易に求められ、ポート１２８を介して連結される可変容積チャンバ１２１内の圧力を用いて、固定容積チャンバ１２９内の圧力を表す。特に、伝達関数は、次のように求められる。

(Volume estimation using intersystem phase)
Similarly, using the same principle, the transfer function is easily determined and the pressure in variable volume chamber 121 connected via port 128 is used to represent the pressure in fixed volume chamber 129. In particular, the transfer function is obtained as follows.

上述のいずれの場合も、本システムの共振周波数は、次のように可変容積Ｖ_２の関数として表され得る。

In any of the above cases, the resonant frequency of the system can be expressed as a function of the variable volume V ₂ as follows:

その他すべてのパラメータが周知であるため、可変容積Ｖ_２は、例えば、共振周波数に基づいて計算可能であるが、Ｖ_２を決定する他の方法も有利である場合があり、本願の過程でさらに説明される。本式において定数ではないパラメータの１つは、音速であり、適正温度の知識に基づいて計算される、あるいは別様に求められる、または測定され得る。

Since all other parameters are well known, the variable volume V ₂ can be calculated, for example, based on the resonant frequency, although other methods of determining V ₂ may be advantageous, Explained. One parameter that is not a constant in this equation is the speed of sound, which can be calculated based on knowledge of the proper temperature, or otherwise determined or measured.

As described above, the volume V ₂ may be determined by employing various strategies and interrogating the system. According to an embodiment of the invention, the system monitors the response of one or more transducers (microphones 1208 and 1209 in FIG. 9) while being excited at a single frequency by drive member 1214. The response is captured as a composite signal and possesses both the amplitude and phase of the pressure fluctuation. It is advantageous that a single interrogation frequency is located in close proximity to the resonance of the system in the intermediate stroke, since a maximum phase change in volume ranging from chamber full to empty is thereby achieved.

The response of the signal microphone 1208 may be corrected to prevent common mode effects due to frequency dependent characteristics of the excitation loudspeaker 1202 (shown in FIG. 6) or the drive member 1214 (shown in FIG. 9). Correction signal obtained as a complex number ratio of the microphone signals may be represented as m _i, where the index i denotes successive time samples of the signal.

  Similarly, when expressed in transfer function form for a second order mechanical Helmholtz resonator, the signal can be expressed as:

ここで、正規化変数が導入され、１のオーダーの計算的有用なダイナミックレンジ内の関連パラメータを維持する。最終式は、公分母上の実数部および虚数部を用いて表される。実数部μの比率を虚数部ｖ（すなわち、位相余接）に当てはめると、次のように求められる。

Here, normalization variables are introduced to maintain relevant parameters within a one order of computationally useful dynamic range. The final expression is expressed using the real part and the imaginary part on the common denominator. When the ratio of the real part μ is applied to the imaginary part v (that is, the phase cotangent), it is obtained as follows.

エラーは、次のように定義され得る。

The error can be defined as follows:

ここで、ＮおよびＤは、それぞれ本モデルの分子と分母を示す。

Here, N and D indicate the numerator and denominator of this model, respectively.

  If the error is minimized for each model parameter, the best fit is achieved. Any method may be employed to adapt to the model parameters. In one embodiment of the present invention, the gradient descent method is employed, and the minimum value is obtained as follows.

各継続時間サンプルが求められる間隔、および時間モデルのパラメータに適合させるためにサンプリングされた間隔数は、本発明の特定の各用途に対し有利に最適化される。定常インスリン送達におけるように、流体がゆっくりではあるが、比較的に定速で流動する場合、τ／３〜３τの期間にかけてサンプリングすることが、有効であることが見いだされている。反対に、比較的に大量の流体のボーラス量が送達される場合、流体は、指数関数的減衰時定数の時間規模に基づいて、ほんの短い間だけ、分注容積チャンバ１２２内に存在してもよい。その場合、サンプリングは、特性減衰時間の短い割合で行われる。

The interval at which each duration sample is sought and the number of intervals sampled to fit the parameters of the time model are advantageously optimized for each particular application of the present invention. It has been found that sampling over a period of τ / 3 to 3τ is effective when the fluid flows slowly but at a relatively constant rate, as in steady state insulin delivery. Conversely, if a relatively large bolus amount of fluid is delivered, the fluid may be present in dispense volume chamber 122 for only a short time, based on the time scale of the exponential decay time constant. Good. In that case, sampling is performed at a short rate of the characteristic decay time.

  According to a preferred embodiment of the present invention, the volume of fluid dispensed through the dispense volume chamber 122 is determined based on a fit to a volume versus time model based on an intersystem phase measurement performed at a monotonic excitation frequency. . Referring to the process diagram shown in FIG. 117, preliminary measurements are taken during the initial portion of the pump stroke and to calibrate the system operation, as will now be described in connection with the measurement protocol. The metrology process, generally indicated by numeral 1170, advantageously saves computer resources and minimizes power consumption, thereby extending the useful time during loading or replacement of power supply 1211 (shown in FIG. 9). On the other hand, through frequent calibration, it provides the measurement accuracy required for the delivery of fluids with the resolution per stroke described above.

  Prior to each pump stroke and / or at the start of 1171, the processor 1210 initiates a self-calibration phase 1172 of the AVS system. The measurement is suspended until the electronic transient due to pump activation is substantially attenuated. In step 1173, the microphone and speaker amplification factors are set and the drive member 1214 is activated at a series of frequencies, but typically is adjacent acoustic region 1290 (otherwise referred to herein as “acoustic chamber”. 5 frequencies are used which are approximately close to the resonance of A frequency in the range of 6-8 kHz is typically employed, but the use of any frequency is within the scope of the present invention. At the start of each continuous frequency start-up, data collection is delayed for about 5 ms until the acoustic transients are substantially attenuated.

  During about 64 acoustic cycles, data is collected as follows. The temperature measurement provided by the temperature sensor 132 (shown in FIG. 70B) is sampled at step 1174 and the real and imaginary parts of the output signal ratio of the signal microphone 1209 to the reference microphone 1208 (denoted by p and ι, respectively). Are sampled. The complex ratio of signals, or other functional combinations of microphone signals relative to a reference microphone, may be referred to herein as “signals” for purposes of describing the AVS system.

  Based on measurements at each frequency for about 200 ms per frequency, a set of average and variance values is determined for each of the real and imaginary parts of the signal at each frequency and the temperature measurement. In step 1175, analysis of these values can determine if there is an error within the specified boundary. Anomalous transfer functions include failures in microphones or other sensors, speakers, transducers, electronics, mechanical components, fluid intrusion, poor acoustic seals, excessive ambient noise, excessive shock and vibration, System failures may be advantageously indicated, but not limited to: Furthermore, the function dependence of the signal phase angle as a function of frequency is determined in step 1176. The signal phase angle, ie, the arc tangent of its imaginary to real ratio, can be used as a phase measurement, however, any phase measurement may be used within the scope of the present invention. The function dependence may be determined by a polynomial fit of phase to frequency or otherwise. Based on or otherwise from the polynomial fit, the slope of the phase versus frequency is determined at the volumetric frequency, and volumetric measurements are made at step 1177. Additionally and significantly, the anomalous slope versus frequency is indicative of fluid bubbles contained within the dispensing chamber 122.

For the subsequent portion of each pump stroke, the drive member 1214 is actuated at a substantially single frequency, thereby acoustically exciting the gas in the acoustically continuous region 1290 at that frequency. Typically, signal data based on the complex ratio of the output signal of the signal microphone 1209 to the reference microphone 1208 is collected and averaged over a specified sampling interval of about 64 cycles. The real and imaginary parts of the signal and temperature data are recorded for each sampling interval. A fit is made to the temporal model based on the sampled and collected data. In various embodiments of the present invention, as described above, during each pump stroke, the errors in fitting the model parameters, ie, the basic volume V _B , peak displacement V _D , and decay time τ of the variable volume chamber 121 are minimized. To limit, a gradient descent method is employed, thereby providing a fluid volume delivered through the dispensing chamber 122.

  Next, referring to FIG. 10, the dispensing spring 130 may have a spiral or fan shape that is complementary to the diaphragm, and may have a plurality of helical grooves 131. The illustrated spring embodiment can apply a substantially equal force to the diaphragm. This substantially equal force helps to maintain a generally concave shape when the diaphragm expands. The groove 131 allows air to freely pass through the spring, so that almost no air is trapped between the spring and the diaphragm.

Referring now to FIGS. 11A and 11B, an example of the volume dynamics measurement of dispense chamber 122 (shown in FIG. 5) and the accumulated volume discharged from dispense chamber 122 is a typical steady state. Shown for delivery pulses (FIG. 11A) and typical bolus delivery (FIG. 11B). As can be seen from FIG. 11A, operation of the pumping assembly 16 causes expansion of the dispensing chamber 122, as measured by the acoustic volume sensor 550, from about 0 to about 1.5 μl in about 2 seconds. Over about 30 seconds with an exponential decay kinetic characterized by a half-life (t _1/2 ) of about 6 seconds, the elastic dispensing chamber 122 contracts and drains the fluid from the chamber 122 through a high impedance output. I understand. It can be seen that the accumulated volume of output from the dispensing chamber 122 is calculated from measurements made by the sensor 550 and increases exponentially to about 1.5 μl. It can be seen that the high impedance output provides a delay between operation of the pump assembly and delivery of the majority of the drained fluid. The t _1/2 characteristic of the system can be selected considering the degree of elasticity and output impedance imparted by the dispensing chamber 122. In various embodiments, the time constant may be varied to save power and eliminate drift problems. The time constant may be, for example, t _1/2 = 2 seconds, ie t _{1 / e} = 2 seconds.

FIG. 11B shows a kinetic profile of bolus delivery of fluid by the fluid delivery device 10. Approximately 29 high-speed continuous pump actuations (ie pulses) each drain fluid from the fluid source to the elastic dispensing chamber 122, thus resulting in a change corresponding to the parameter measured by the acoustic volumetric sensor 550. It can be seen that the volume of the dispensing chamber 122 is expanded to about 1.5 μl by the first pump pulse and is similar to the value observed in FIG. 11A. The volume of the dispensing chamber 122 is further expanded by additional pulsating pumping with a pulse interval that is shorter than the time required to achieve full discharge of the dispensing assembly 120. Expansion reaches up to about 6 μl. It can be seen that the cessation of the pump pulsation occurs after about 85 seconds and the volume of the chamber 122 decreases with exponential decay kinetics, resulting in a complete release of its content by about 30 seconds after stopping the pumping. This final release t _1/2 is approximately the same as for the steady delivery shown in FIG. 11A. It can be seen that the calculated accumulated output volume rises with approximately linear dynamics during pumping and becomes stagnant due to pumping outage.

  In the described system, fault conditions are detected by volumetric measurement rather than by pressure measurement, and therefore the fault can be determined in seconds. FIGS. 11C-11F show various detection failure conditions by sensor 550 of FIGS. All descriptions for FIGS. 11C-11F will be described with reference to FIGS.

  FIG. 11C shows the output dynamic profile over time of the pumping pulse of sensor 550 under normal operating conditions. In contrast, FIG. 11D shows the expected result of occlusion downstream of the dispense assembly 120. An increase (or non-decrease) in the fluid volume within the dispensing chamber 122 is quickly detected by the sensor 550.

  The low volume state is shown in FIGS. In FIG. 11E, a substantially maximum sensor signal is achieved, followed by excessive fast decay. This condition may indicate an internal leak in pump 16, line 310, or dispense assembly 120. The kinetic profile of FIG. 11F has a low peak volume signal and may be a representation of a pump failure, an empty reservoir 20, or an occlusion upstream of dispense chamber 122. Also, delayed expansion of the dispensing chamber 122 relative to pump operation may indicate a problem with the flow line 310. The sensor 550 may be capable of detecting bubbles in the fluid. The alarm can be activated in response to detection of a fault condition.

  FIG. 12 shows a process diagram depicting the acoustic volume sensing and compensation cycle (corresponding to the control loop 360 of FIGS. 2A-3). The sensor may measure the amount of fluid dispensed from the device 10 based on measuring the magnitude of the cycle change in the variable volume chamber 121 induced by the pumping cycle. For example, the sensor 550 repeatedly acquires the acoustic spectrum of the resonant variable volume 121 and the reference volume chamber 127 (step 2611) and updates the parameters (updated for each pumping pulse to reduce the volume of gas in the variable volume chamber 121). Embedded) may be maintained.

  Thus, the updated parameter indicates the net amount of fluid that has entered the dispensing chamber 122. If there is a sufficient delay between pulses, the fluid entering the dispensing chamber 122 is approximately equal to the volume dispensed by the device 10. Alternatively, the sensor 550 can repeatedly measure an increase in the volume of gas in the variable volume chamber 121 to determine the amount dispensed by the device (if there is sufficient delay between pulses). . The acoustic spectrum is compared to a model spectrum in a look-up table, which may correspond to some or all of the dispensing chamber 122, with bubbles, without bubbles, or with various sized bubbles (step 2621). The lookup table may hold data that has been experimentally obtained, determined using a model, or determined to work empirically. The lookup table may include data representing various bubble-containing states and / or normal states for the multi-expansion degree of the dispensing chamber 122. If the spectrum and updated total value fit the normal flow model (step 2631), then in step 2611 another acoustic spectrum is acquired and the cycle is repeated. If the spectrum and / or the updated sum does not fit the normal flow model, the presence of low or occluded flow is determined (step 2641). Low flow or occluded flow may be indicated by a sustained out-of-range volume of the variable volume chamber 121, by an updated sum below a predicted or set value, or both. When a low flow or occluded flow condition is detected, an alarm is triggered (step 2671). Alarms may include audible signals, vibrations, or both. If a low flow or occluded flow condition is not found, the device determines whether the spectrum fits a model corresponding to the condition of bubbles in dispense chamber 122 (step 2661). If it is determined that bubbles are present, a response is initiated (step 2651) that may include an alarm and / or compensation action, which may include temporarily increasing the pumping rate, and in step 2611 the cycle is resumed. . If it is determined that no bubbles are present, an alarm is triggered to indicate an unknown fault condition (step 2671). Embodiments of the present invention also utilize bubble detection using AVS technology as disclosed in co-pending US Patent Application No. 60 / 789,243 (incorporated herein by reference). May be.

  The pumping assembly 16 of FIGS. 2A-3 biases fluid from the reservoir 20 to the dispensing assembly 120. When the dispensing assembly according to FIGS. 6-7 is used, the feedback provided from the dispensing assembly 120 to the pumping assembly 16 allows adjustment of the pumping assembly 16 based on an accurate measurement of the volume delivered, There is no need to use a high precision pump. Individual pumping pulses may be sufficiently low in capacity to allow fine compensation based on feedback. Thus, many different pumping assembly 16 implementations can be employed. Various possible embodiments of the pumping assembly 16 are described below.

  Figures 13 and 14 schematically illustrate alternative embodiments of some components within a fluid delivery device, according to embodiments of the present invention. FIG. 13 shows a flow line 310 with a pumping assembly 16 having a pumping element 2100 positioned between an upstream one-way valve 21 and a downstream one-way valve 22. The pumping element 2100 may use an actuator to deform a portion of the flow line and generate pressure in the flow line 310. Upstream one-way valve 21 prevents backflow from pumping element 2100 to a fluid source (not shown), and downstream one-way valve 22 prevents backflow from volume sensing chamber 120 to pumping element 2100. As a result, the fluid is driven in the direction of the outlet assembly 17 and in one embodiment includes a high impedance path.

  In the alternative embodiment shown in FIG. 14, the function of the pumping element, ie, the function of generating pressure in the flow line 310 and the function of the upstream one-way valve 21 are performed by the combined valve pump 2200. Accordingly, the pumping assembly 16 of the embodiment of FIG. 14 consists of two components (ie, a combined valve pump 2200 and a downstream one-way valve 22) instead of the three components used in the embodiment of FIG. . Other embodiments of the pumping assembly 16 may be used. The combination of the valve function and the pumping function in the valve pump 2200 may be achieved by various mechanisms, some of which are described below with reference to FIGS. 15A-16 and 22-56.

  In many embodiments described below, the poppet of the inlet valve 21, the poppet of the outlet valve 22, and the pumping actuating member 54 are all directly or indirectly (eg, as in FIGS. 50-56). By communicating with line 310, each of these elements can generate or react to various fluid pressures. As mentioned above, the upstream and downstream valves (sometimes referred to herein as inlet and outlet valves) are one-way valves. The valve can be a crater valve, a flap valve, a check valve, or a duckbill valve, among other types of one-way valves, i.e., other types of valves that bias flow to the device output. An example of a crater valve was developed on December 12, 1993 by Dean L. No. 5,178,182 issued to Kamen (incorporated herein by reference).

  In the embodiment shown in FIGS. 15A-15D, the pumping assembly includes both an inlet valve 21 and an outlet valve 22, respectively, a fluid inlet, a fluid outlet, and a movable member (a membrane for each valve). 2356). The pumping assembly also includes a pumping element 2100. The pumping element is located downstream from the inlet valve 21 and upstream from the outlet valve 22. In the following description, the outlet valve starts from a closed position, i.e. a position where no fluid flows to the outlet valve. However, if the fluid presents sufficient pressure, the pressure to open the valve is applied to the membrane and outlet valve poppet 9221, thereby opening the outlet valve with fluid pressure, and thus the fluid is discharged to the outlet valve 22. It becomes possible to flow to. The embodiment of FIGS. 15A-15D is a combined valve pump (such as element 2200 of FIG. 14) in the sense that it closes the pump inlet by a single mechanical action and then biases the flow to the pump outlet. May be considered to be.

  This pumping arrangement has the advantage of dividing the moving parts and the wetted line components on the opposite side of the flexible barrier membrane 2356. As a result, the movable part can be located in a reusable component and the wetted part (fluid line 310) can be located in a disposable component.

  In a preferred embodiment of the pumping mechanism, the fluid source is a non-pressurized reservoir. When the inlet valve movable member is in the open position and there is a negative pressure in the pumping chamber, there is a pressure differential that draws fluid from the reservoir to the inlet valve. This negative pressure can be caused by the elasticity of the membrane in the pumping chamber. In an alternative embodiment, a spring (which may be embedded in the membrane) may be used to assist in recoiling the membrane in the pumping chamber. The non-pressurized reservoir may be foldable so that its volume is reduced by a corresponding contraction in the reservoir as fluid is drawn from it. As a result, negative pressure or air accumulation in the reservoir is prevented.

  In a preferred embodiment of the pumping mechanism, after the inlet valve is closed, pressure is applied to the pumping chamber to force fluid from the pumping chamber to the outlet valve. The pressure generated by the pumping motion opens the outlet valve, causing fluid to flow to the fluid outlet of the outlet valve.

  The movable member can be any that can function as described above. In some embodiments, the movable member is a flexible membrane or an elastic pumping diaphragm. In other embodiments, the movable member is a ball-shaped rigid structure or another object capable of preventing fluid outflow from an opening in the fluid path.

  In practice, the pumping mechanism may be primed prior to use. Thus, the pumping mechanism repeatedly removes air from the fluid line several times until most or all of the air in the fluid line is removed. Many pumping mechanisms disclosed herein have the ability to “auto-prime” because of the small fluid volume contained outside the pumping chamber (except between the valves). When the pump pressurizes air into the pump chamber, it generally accumulates enough pressure to blow through the outlet valve. Thus, a subsequent return stroke can generate sufficient negative pressure on the pump to draw liquid from the reservoir. If the “dead” volume of the pump is too large, the air in the pumping chamber may not accumulate enough pressure to escape from the outlet valve. As a result, the pump can stall.

  Figures 15A-15D, 16, and 22-56 show some embodiments of the pumping mechanism. Referring now to FIGS. 15A-15D, an embodiment of a pumping mechanism is shown that illustrates several steps in the pumping process. 1. Fluid passes through the inlet valve 21 (as shown in FIG. 15B). 2. The inlet valve is closed (as shown in FIG. 15C). 3. A pumping actuating member 54 urges fluid in the downstream direction, causing fluid pressure to open the outlet valve 22 and flow to the fluid outlet (as shown in FIG. 15D).

  The pumping mechanism of FIGS. 15A-15D includes a movable member, but in this embodiment is a part of the flexible membrane 2356. The inlet and outlet valves include poppets 9221, 9222 that function as valve occluders. Poppets 9221, 9222, and pumping actuation member 54 include springs 8002, 8004, 8006, respectively. The pump plate 8000 is attached to both the pumping actuating member 54 and the inlet poppet 9221 and serves as an end for the respective springs 8004, 8002.

  The term “poppet” is used to indicate a member that applies pressure to a movable member (ie, the membrane) and affects the position of the membrane. Although other designs may be used, specific examples of some of the spring-loaded poppet valves that utilize the mechanical advantage structure and principles are described below (in conjunction with FIGS. 50-56). However, mechanisms other than poppets can be used to perform the same function. 15B-15D, the inlet valve 21 includes a fluid inlet, a fluid outlet, a portion of the membrane 2356, and a poppet 9221. The outlet valve 22 includes a fluid inlet, a fluid outlet, a portion of the membrane, and a poppet 9222.

  In the embodiment shown in FIGS. 15A-15D, the fluid path 310 may have a structure (element 9310 in FIG. 15A) that may have a stiffness or some flexibility (preferably less flexible than the membrane 2356). Specified by. As shown in FIG. 15A, the housing structure 9310 defines valve chambers 9321, 9322 and a pumping chamber 2350. All three of these chambers are in the fluid path 310.

  Referring now to FIGS. 15B-15D, the inlet valve 21, outlet valve 22, and pump element 2100 each have a fluid inlet and a fluid outlet. The pumping actuating member 54 has a pumping chamber 2350 through which fluid flows after flowing out of the inlet valve. The pumping actuation member 54 applies pressure to the membrane 2356 and creates a positive pressure in the fluid line.

  As shown in FIGS. 15B-15D (and similarly for the valve seat 4070 of the outlet valve shown in FIGS. 50-56), the valve seat 9121 in the inlet valve 21 is made of a membrane. When not actuated by valve poppet 9221, it is preferably spaced from membrane 2356.

  Fluid line 310 is defined in part by membrane 2356. In this embodiment, membrane 2356 separates the pumping mechanism components from the fluid. Therefore, the fluid line 310 is in contact with the fluid, and the pumping actuator 54 and the valve poppets 9221 and 9222 are not in contact with the fluid. However, alternative embodiments of the pumping assembly need not include the membrane 2356 in contact with the fluid line 310. Alternatively, different movable members may be used for the valves and / or pumps. In still other embodiments, only parts of the fluid line 310 are separated from the pumping mechanism and thus partially wet the pumping assembly.

  Inlet poppet 9221 includes an end 8018 that indicates the surface area of the inlet poppet that contacts the membrane portion of fluid line 310. The pumping actuation member 54 includes an end 8012 that contacts the membrane portion of the fluid line 310. Similarly, the outlet poppet 22 includes an end 8022 that contacts the membrane portion of the fluid line 310. Valve poppet ends 8018, 8022 apply pressure to respective regions of the membrane 2356 to block or unblock respective portions of the flow path 310. Also, the pressure actuating member ends 8012 create a flow through the fluid line 310 by applying pressure to the respective regions of the membrane.

  The pumping operation member 54 is provided around a plunger bias spring 8004. Plunger bias spring 8004 has both the ends of pump plates 8000 and 8014 and a support structure that also holds the pumping actuation member.

  The inlet poppet 21 is perimetered by an inlet poppet spring 8002, but in an alternative embodiment, the inlet poppet itself is elastic and performs the function of a spring. Inlet poppet spring 8002 has both the end of pump plate 8000 and the proximal end 8018 of inlet poppet 9221.

  The outlet poppet 9222 is circumferentially provided by a passive outlet poppet spring 8006. Outlet poppet spring 8006 has both an end of outlet poppet plate 8024 and an edge 8020 near the end of outlet poppet 9222.

  In each case, springs 8002, 8004, 8006 terminate in front of their respective ends and do not interfere with surface regions 8018, 8012, 8022 that contact membrane 2356.

In a preferred embodiment, the fluid pumping device also includes at least one shape memory actuator 278 (eg, a conductive shape memory alloy wire) that changes shape with temperature. The temperature of the shape memory actuator may be changed by a heater or, more conveniently, by application of current. 15B-15D illustrate an embodiment with one shape memory actuator 278, however, other embodiments (described below) may have more than one shape memory actuator 278. In one embodiment, the shape memory actuator is a shape memory wire comprised of a nickel / titanium alloy such as NITINOL ^™ or FLEXINOL®. However, in other embodiments, any device capable of generating a force, such as a solenoid, can be used. In one embodiment, shape memory actuator 278 has a diameter of about 0.003 inches and is about 1.5 inches long. However, in other embodiments, the shape memory actuator 278 is made of any heat shrinkable alloy (expansion is assisted by a mechanism that applies a force to the alloy and stretches the alloy to its original length, ie, a spring. Although such a mechanism may not be required), a pumping mechanism as described in the embodiments herein may be activated. In certain embodiments, the shape memory actuator 278 has a diameter from 0.001 inch to any desired diameter, and the length can be any desired length. In general, the larger the diameter, the greater the available contraction force. However, the current required to heat the wire generally increases with diameter. Accordingly, the diameter, length, and composition of the shape memory alloy 278 can affect the current required to operate the pumping mechanism. Regardless of the length of the shape memory actuator 278, the actuation force is substantially constant. An increase in actuation force can be imparted by increasing the diameter of shape memory actuator 278.

  Shape memory actuator 278 connects to pump plate 8000 through connector 8008. Connector 8008 is described in detail below. The shape memory actuator 278 connects to the fluid pumping device via a terminal connector 8010. Depending on the device or system in which the pumping mechanism is used, the termination connection position will vary. Termination connector 8010 is described in detail below.

  15B-15D show the pumping mechanism and fluid line 310 already primed as described above. Referring now to FIG. 15B, the inlet valve 21 is open and the pumping actuation member 54 is not in pressure contact with the membrane 2356. The outlet valve 22 is in the closed position. Shape memory actuator 278 is in the extended position. In this configuration, fluid is drawn from a reservoir (not shown) to the inlet valve 21 fluid inlet. (Although shown as a bulge in the membrane of the inlet valve region, the step of attracting fluid in this step can cause a recess in the membrane, ie, no deformation of the membrane.) The inlet poppet is in the open position. In some cases, fluid can flow from the fluid inlet to the fluid outlet and further into the pumping chamber 2350. At this point, the outlet poppet end 8022 presses firmly against the membrane 2356 and seals the outlet valve 22.

Referring now to FIG. 15C, current is applied to the shape memory actuator 278, and the shape memory actuator is contracted from the starting length to the desired end length. The contracting step of the shape memory actuator 278 draws the pump plate 8000 to the fluid line 310. Inlet poppet 9221 and pumping actuating member 54 are both connected to pumping plate 8000. The movement of plate 8000 draws both inlet poppet 9221 and pumping actuating member 54 to membrane 2356. As shown in FIG. 15C, the inlet poppet end 8018 is firmly pressed against the membrane 2356, sealing the membrane against the valve seat 9121 and closing the inlet valve 21. (The movement of the inlet poppet can energize a small amount of fluid in the inlet valve chamber (element 9321 of FIG. 15A) through either the fluid inlet or the fluid outlet of the inlet valve 21.)
At the same time, the pumping actuation member 54 begins its path to the pumping chamber 2350. During this process, when inlet poppet spring 8002 is compressed (at this point, inlet poppet end 8018 is in firm contact with fluid line 310), pump plate 8000 and pumping actuating member 54 are Continue moving to fluid line 310. The inlet poppet spring 8002 allows the pump plate 8000 to continue to move to the fluid line 310 with the pumping actuating member 54 even if the inlet poppet 9221 cannot move further.

  Referring now to FIG. 15D, the pumping actuation member 54 presses against the region of the membrane 2356 on the pumping chamber 2350 and the fluid is pumped to increase the pressure of the fluid in the pumping chamber 2350. The outlet poppet end 8022 remains firmly pressed against the membrane 2356 (assisted by the outlet poppet spring 8006) until the outlet valve 22 is opened by pressure from the fluid flowing from the pumping chamber 2350. The fluid inlet and the fluid outlet are sealed. When sufficient pressure is reached, fluid flows out to the fluid outlet of the outlet valve 22 and thus overcomes the pressure applied to the membrane 2356 by the outlet valve 22. By stopping the flow, the outlet valve 22 is closed by a passive spring 8006.

  During the working stroke, the pumping actuating member spring 8004 is loaded. Ultimately, the pumping actuation member spring 8004 pulls the pumping actuation member 54 away from the membrane 2356. As a result, during the relaxation stroke, spring 8004 returns pumping actuating member 54 and pumping plate 8000 returns to the relaxed position of FIG. 15C. The loaded inlet poppet spring 8002 may also provide energy for the return stroke. When the pumping plate 8000 approaches its relaxed position, it engages with the cap of the inlet poppet 9221, lifts the inlet poppet and disengages it to open the inlet valve 21. Pumping actuating member spring 8004 is also unloaded during the return stroke.

  Pump plate 8000 unloads from pumping actuating member spring 8004 when inlet poppet spring 8002 reaches a threshold distance that is at the same level as pump plate 8000. The membrane 2356 in the pumping chamber 2350, which is elastic, returns to its starting position. This creates a negative pressure and when the inlet valve opens, fluid flows from the fluid inlet of the inlet valve to the fluid outlet and further to the pumping chamber 2350. Accordingly, the pumping mechanism is in a state as shown in FIG. 15B.

  The entire pump sequence described with respect to FIGS. 15B-15D is repeated each time the pump is activated by applying current to the shape memory actuator 278.

  The membranes referenced herein, including membrane 2356, may be made from any elastic material that can provide the necessary properties to function as described herein. Further, the membrane material may include a biocompatible material so that it does not interfere with pumping or reduce the therapeutic value of the fluid. A plurality of biocompatible elastic materials may be suitable, including nitriles and silicones. However, different therapeutic fluid compositions require the selection of different elastic materials.

  The pumping mechanism described above and the various embodiments described herein can be described in terms of stroke length. One method of determining the stroke length is by the total change in the length of the shape memory actuator during one cycle of shape memory actuator contraction and expansion. This difference determines the total distance traveled by the pump rod, and thus the total amount of fluid that has flowed from the inlet chamber 2354 to the pumping chamber 2350, further to the outlet chamber 2352, and ultimately from the outlet chamber 2352. Another way to determine the stroke length is the travel distance of the pump plate 8000. For a partial stroke, the pump plate 8000 does not reach its maximum travel distance. In one embodiment, small or minute strokes are continuously initiated to continuously or periodically pump microliter volumes of fluid from the reservoir to the outlet. For example, the microstroke may displace the volume of the pumping chamber 2350 by less than 20%, 10%, or 1%.

  FIG. 16 shows a modification of the embodiment of the pumping mechanism shown in 15B. In FIG. 16, two different shape memory actuators (long and short) are used. FIG. 16 shows an embodiment of the pumping mechanism shown in FIG. 15B, where shape memory wire 278 is stretched around pulley 286 and split into long and short fiber bundles. The common joint serving as a negative terminal may be located at a place where the long and short fiber bundles are split. Completion of a circuit having either or both of the alternative paths allows adjustment of pumping force and / or stroke length. In an alternative embodiment, a portion of the material, such as a Kevlar material, extends from the common joint around the pulley to the force plate 8000, and two separate shape memory wire portions are respectively connected from the common joint. Extends to the support. These embodiments provide both a pumping mode and an air exhaust mode by using two wires having different lengths, as described below.

  For variable strokes that use shape memory actuator variables for a given length of shape memory actuator, the stroke depends on several variables. 1. 1. Total number of hours that electricity / heat is applied 2. the total voltage of electricity, and The diameter of the shape memory actuator. Some variable embodiments are shown in FIGS. However, in some embodiments, the stroke is variable while maintaining length, current time, and voltage. These embodiments include multiple shape memory actuators (see FIG. 19) and multiple switches on a single shape memory wire (see FIG. 17). Also, as described above, the desired stroke length can be achieved by modifying any one or more variables.

  Furthermore, it is possible to control the stroke by changing the timing at which heat or current is applied to the shape memory actuator. Each time the shape memory actuator is heated may be referred to as a pulse. Factors such as pulse frequency, pulse width, and stroke length can affect the amount of fluid delivered over time.

  17-19 further depict an embodiment of a pumping assembly having both a fluid pumping mode and an air rejection mode. When activated, the air rejection mode utilizes a compression stroke with an increased displacement and / or an applied force by an increased force member. The air rejection mode may be triggered based on the possibility or recognition of air present in the pumping assembly. For example, the air exclusion mode may be triggered when a line is attached to the reservoir, when bubbles are detected by the sensor or sensing instrument, or when insufficient flow is detected by the sensor or sensing instrument. Alternatively, two modes may be used to discharge a smaller or larger fluid volume for a given pumping pulse.

  Referring now to FIG. 17, a schematic diagram shows a pumping assembly activated by shape memory actuator 278 and having multiple modes of operation. When the pumping chamber 2350 is filled with fluid, the pumping assembly operates in a fluid pumping mode. During the fluid pumping mode, current flows between the cathode conductor 2960 and the anode conductor 2961 resulting in resistive heating of the alloy shape memory actuator 278 and the resulting phase change and power stroke. In one embodiment, during the priming step of the pumping mechanism, or if the presence of a bubble 2950 is suspected in the pumping chamber 2350, the air evacuation mode is triggered and the current is between the cathode conductor 2960 and the anode conductor 2965. It flows along the path of the extended length. The result is a compression stroke with a greater force on the force member 2320 and its displacement sufficient to discharge air 2950 from the pumping chamber 2350 to the pump outlet 2370. In alternative embodiments, the anode and cathode conductors may be reversed.

  Referring now to FIG. 18, a schematic diagram shows an alternative pumping assembly having a plurality of shape memory actuators 278 of the same length. Additional actuators may be used to increase the operating pressure on the pumping chamber 2350, for example, to remove a blockage or bubble in the fluid line, pumping chamber, or other area of the pumping mechanism. Additional actuators may also provide surrogate functionality for any pumping device. The single shape memory actuator may be capable of applying sufficient force to remove bubbles from the pumping chamber. Further, in the embodiment shown in FIG. 18, an additional return spring may be necessary depending on the length of the second shape memory actuator.

  When the reservoir is initially attached to a flow line having a pumping assembly, the pumping mechanism (element 16 in FIGS. 13-14) is typically filled with air. Also, air can enter the pumping mechanism during normal operation for a variety of reasons. Because air is more compressible than fluid, if there is a significant amount of air in the fluid line, applying a compression stroke long enough to expel the fluid is the cracking pressure of the one-way valve of the pumping mechanism. It may be insufficient to generate enough pressure to overcome Hence, the pumping mechanism can stall. However, it may be desirable to energize the air through the line during priming or if there is a small amount of air in the pumping assembly that has no effect. Thus, in this situation, it is possible to apply additional force using the embodiment shown in FIG.

  FIG. 19 schematically illustrates an alternative pumping assembly 16 having a plurality of shape memory actuators. The first shorter shape memory actuator 2975 has a first conductor 2976 and a second conductor 2777. The short actuator 2975 can produce a sufficient compression stroke to drain the fluid in the pumping chamber 2350. The shorter shape memory alloy actuator 2975 is typically used during fluid pumping mode operation. When air rejection mode is indicated, or when a larger pumping fluid volume is needed, by sending current along the actuator length disposed between the first conductor 2993 and the second conductor 2972 A second shorter shape memory alloy actuator 2970 may be used. The longer shape memory alloy actuator 2970 is also used as an auxiliary actuator for fluid pumping mode operation by creating a short circuit including an electrical path between the first conductor 2972 and the second conductor 2971. May be. The shorter shape memory actuator 2975 may also be used to vary the stroke volume and provide better control at low fluid volume. The multi-mode actuators of FIGS. 17-19 are not limited to use with the illustrated pump components, and may be employed with any of the various embodiments of the pumping mechanism described herein, as described below. The thing using a pumping apparatus and the thing which employ | adopts the valve pump mentioned later are included. Thus, the desired stroke length can be initiated by applying electricity / heat to the shape memory actuator length that provides the desired stroke length.

  Referring now to FIGS. 20A and 20B, one embodiment for attaching a shape memory actuator, respectively, is shown. These various embodiments can be used in any mechanism or apparatus described herein that employs a shape memory actuator 278. Referring to both FIGS. 20A and 20B, shape memory actuator 278 is fed into grommet 280. Next, the grommet 280 is attached to the part 284. Although only two embodiments are shown for this mode of attachment, various other modes are used in other embodiments. Other ways of attaching the grommet to the part or any fixed position can also be used.

  Referring now to FIGS. 21A and 21B, two exemplary embodiments of attaching a shape memory actuator 278 for use with the pumping mechanism 16 are shown. In each of these embodiments, shape memory actuator 278 is designed to pivot about pulley 286. Referring to FIG. 21A, the shape memory actuator 278 is attached to a piece 288 preferably made of Kevlar material via a grommet 280. One end of shape memory actuator 278 is shown attached to part 284 by a set of screw fasteners 289. Referring now to FIG. 21B, one end of the shape memory actuator is shown attached to part 284 by grommet 280.

  Various embodiments of the pumping mechanism are shown herein. The pumping mechanism may include an inlet valve, a pumping actuation member, and an outlet valve. As mentioned above, different types of one-way valves may be used in alternative embodiments. The schematics shown in FIGS. 15A-15D illustrate one embodiment, but the following figures illustrate alternative embodiments.

  Next, referring to FIG. 22 and FIG. 23, a side view and a sectional view of one section of the pumping mechanism portion are shown. In this embodiment, the pumping actuation member is an elongated pumping finger 32. When a force is applied to the finger part 32, the finger part 32 presses against the movable member, and reduces the internal volume of the fluid line. The pumping mechanism portion of FIGS. 22 and 23 shows only the pumping chamber. When the one-way valves (elements 21 and 22 in FIG. 13) are coupled, application of deformation force to the movable member 23 causes fluid to flow to the outlet assembly (not shown). As shown in FIGS. 22 and 23, the finger 32 is pointed to concentrate force, but in other embodiments, the finger 32 is flat or any other suitable shape. Also good. The spring 31 serves to return the finger 32 to the contracted non-pressed position when no force is applied by biasing the finger 32 to the contracted position with respect to the elastic member 23. As shown in FIG. 23, it is possible to apply force to the finger portion 23 using a motor. However, in other embodiments, shape memory actuators are used. Various types of motors are suitable, including electric motors and piezoelectric motors.

  Referring to both FIGS. 22 and 23, the anti-reverse device 33 restricts the potential movement of the finger 32, supports the movable member 23, and is fixed from the movable member 23 in response to the application of force by the finger 32. Preventing displacement from position ensures volume reduction in the fluid line or pumping chamber. As can be seen from FIG. 22, the anti-reverse device 33 may advantageously have a complementary shape to the elastic member 23. In various embodiments, the pumping assembly 16 may include a lever or crank that is driven at one end by a motor and compresses the elastic member 23 at the other end.

  Referring now to FIG. 24, another embodiment of a pumping actuation member is shown in connection with a portion of the pumping assembly. A motor or shape memory actuator (not shown) applies a rotational force to the group of connected projections 42. These protrusions 42 serve as a pumping operation member, and further apply force to the movable member 23 in order. Therefore, an intermittent pulse of force is applied to the movable member 23. As shown in the drawing, the reverse rotation preventing device 33 is movable in the housing 44 and is biased upward to the elastic member 23 by a spring 46.

  Referring now to FIG. 25, an embodiment of a force assembly comprising a pumping actuation member (here, a plunger) 54 within the outer cylinder 52 is shown. The plunger 54 is alternately pulled back by the motor and inserted into the outer cylinder. When the plunger 54 is pulled back, negative pressure draws fluid from the reservoir (not shown) into the channel 51 and lumen 56. When the plunger 54 is inserted, the increased pressure in combination with the one-way valve (not shown) drives fluid to the dispensing assembly (not shown). The lumen 56 is connected to the channel 51 via the connecting channel 58 and the volume of the outer tube lumen 56 decreases with the plunging action of the plunger 54, thereby energizing the fluid to the flow line 310.

  FIGS. 26 and 27 show another embodiment in which the pumping actuating member is a plunger 54. A force assembly and a linear actuator including shape memory actuator 278 drive plunger 54. In FIG. 26, the shape memory wire 278 is in a cooling expansion state, and is attached to the first support portion 241 and the plunger attachment cap 244. The cap 244 is further attached to a bias spring 243 attached to the second support portion 242 in order. When the wire 278 is in the expanded state, the bias spring 243 is in the relaxed state. FIG. 27 shows the shape memory actuator 278 in a contracted state by applying current to the wire 278 and simultaneous heating. In response to the contraction, a force is applied to the cap 244, causing an insertion movement of the plunger 54 and a corresponding pumping action. In the contracted state, the bias spring 243 is in a high energy latent state. In response to the stop of application of the magnetic field, the nitinol wire 278 cools and expands again, causing the bias spring 243 to return the plunger 54 to its contracted state. As shown in FIGS. 21A-21B, the shape memory actuator 278 may be wound around one or more pulleys.

  FIGS. 28-30 illustrate various embodiments in which pumping is accomplished by the pumping actuation member 54 using a shape memory actuator 278 to compress the movable member that forms the pumping chamber. The pumping chamber is bounded by one-way valves 21, 22. FIG. 28 shows an embodiment including a pumping mechanism in which the pumping actuating member is a plunger 54 in the outer cylinder 52. The mechanism also includes a lever 273, a fulcrum 274, and a shape memory actuator 278. The shape memory actuator 278 is held in the housing 298 and has one end attached to the conductive support 279 and the other end attached to the positive potential 275 of the lever 273. The lever 273 is further attached to the fulcrum 274 at the center and the plunger 54 at the second end. A current is applied to cause current to flow through terminal 275, shape memory actuator 278, and conductive support 279, thereby causing shape memory actuator 278 to contract, causing lever 273 to pivot about fulcrum 274, and Causes pullback. Stopping the current causes the shape memory actuator 278 to cool and expand. The return spring 276 acts via the lever 273 to return the plunger 54 to the insertion position in the outer cylinder 52. The return spring 276 is held in the housing 277. The O-ring 281 prevents fluid leakage of the plunger 54 / cylinder 52 assembly. The insertion and withdrawal of the plunger 54 causes the fluid flowing through the flow line to flow in a direction determined by the orientation of the two check valves (first one-way valve 21 and second one-way valve 22). Any suitable backflow prevention device may be used, including one-way valves, check valves, duckbill valves, flapper valves, and crater valves.

  FIG. 29 shows another embodiment of a pumping mechanism having a plunger 54, an outer cylinder 52, and a force assembly that includes a shape memory actuator 278. However, unlike the embodiment shown in FIG. 28, this embodiment does not include a lever. The shape memory actuator 278 is held in the housing 298, and one end is attached to the conductive support portion 279 and the other end is attached to the plunger cap 244 by the contact 275. The plunger cap 244 is attached to the plunger 54. When sufficient current is applied through contact 275, shape memory actuator 278 contracts. This contraction pulls the plunger cap 244 and causes the plunger 54 to be inserted into the outer cylinder 52. Stopping the current causes the shape memory actuator 278 to cool and thereby expand. In response to the expansion of the wire, the return spring 276 acts to return the plunger 54 to the retracted position in the outer cylinder 52. The return spring 276 is held in the housing 277. O-ring 281 prevents fluid leakage from plunger 54 / cylinder 52 assembly. The insertion and withdrawal of the plunger 54 causes the fluid flowing through the flow line to flow in a direction determined by the orientation of the first one-way valve 21 and the second one-way valve 22.

  Referring now to FIG. 30, an embodiment of a pumping device that uses a plunger 54 and an outer cylinder 52 is shown. In this embodiment, a shape memory actuator 278 in the form of a wire positioned on a shaft within the plunger 54 is used to apply a force to the plunger. Shape memory actuator 278 extends from plunger cap 272 to the shaft in plunger 54 and from channel 58 to support base 299. O-rings 281 and 282 seal the plunger 54, the outer cylinder 52, and the channel 58. By applying a current to the first conductor 258 and the second conductor 257, the shape memory actuator 278 is heated, and the shape memory actuator 278 contracts. The contraction of the shape memory actuator 278 generates a downward force sufficient to overcome the upward biasing force of the return spring 276 applied to the plunger cap 272, thereby causing the plunger 54 to move into the lumen 290 of the outer cylinder 52. To drive. By expansion of the shape memory actuator 278, the return spring 276 returns the plunger 54 to the retracted position. The insertion and withdrawal of the plunger 54 causes the fluid flowing through the flow line to flow in a direction determined by the orientation of the first one-way valve 21 and the second one-way valve 22.

  An alternative embodiment of the pumping mechanism is shown in FIG. The pumping actuating member is an assembly 101 that combines the functions of the reservoir and the pumping mechanism. Based on the command of the controller 501, the motor 25 drives the plunger 102 and generates pressure in the reservoir 104, thereby energizing fluid to the first one-way valve 106. The fluid then flows from the elastic dispensing chamber 122 of the volume sensor assembly 120 having the sensor 550 to the outlet assembly 17. An optional second one-way valve 107 may be included. Feedback control between the sensor 550 and the motor 25 via the controller 501 ensures the desired flow rate of fluid to the patient. The first one-way valve 106 serves to prevent reverse flow of fluid due to the elastic force of the dispensing chamber 122 of the volume sensor assembly 120 when the chamber is filled and expanded. The second one-way valve 107 serves to prevent reverse flow of fluid from the outlet assembly 17 or the patient 12 to the dispensing chamber 122. In this embodiment, the sensor 550 can immediately detect the volume in the dispensing chamber 122.

  32-34 schematically show a cross-sectional view of the combined valve pump 2200. FIG. 32 shows a valve pump 2200 having a collection chamber 2345 and a pumping chamber 2350 in a rest position prior to operation. FIG. 33 shows the valve pump 2200 in operation during the compression stroke. FIG. 34 shows the pump in the activated state at the end of the compression stroke. The pump inlet 2310 is in fluid communication with an upstream fluid source such as a reservoir and is connected to the first end of the channel 2360. A channel 2360 connects at a second end with a collection chamber 2345 that is in fluid communication with a diaphragm opening 2390 disposed within the elastic pumping diaphragm 2340. The collection chamber 2345 is bounded on the first side by an elastic pumping diaphragm 2340 and on the second side by an elastic pumping membrane 2330. The pumping membrane 2330 may be made of latex or silicone rubber, among others. The downstream side of the diaphragm opening 2390 opens to the pumping chamber 2350. During the pump priming step and during the working cycle, fluid moves from a fluid source, such as a reservoir, to a pump inlet 2310, a channel 2360, a collection chamber 2345, and a diaphragm opening 2390, and then in the pumping chamber 2350. To reach. The one-way valve 22 allows fluid to flow out of the pumping chamber 2350 through the pump outlet 2370 until sufficient fluid pressure is applied to the one-way valve 22 and the one-way valve 22 is opened and is not opened. To prevent. In FIG. 32, the pumping actuation member 2320 is shown in a rest position and the elastic pumping membrane 2330 is shown in a minimum surface area relaxed configuration, thereby maximizing the volume of the collection chamber 2345. In this embodiment, the pumping actuation member is shown as a ball, but in other embodiments, the pumping actuation member can be actuated to actuate the pumping mechanism and apply sufficient force to the elastic pumping membrane 2330. Can be any.

  As can be seen from FIG. 33, during the compression stroke, when the pumping actuating member 2320 is actuated, the pumping actuating member 2320 begins to move to the diaphragm opening 2390 of the elastic pumping diaphragm 2340, causing the elastic pumping membrane 2330 to expand and the collection chamber. This causes a back flow of the fluid collected in 2345. In the latter half of the applied stroke, as shown in FIG. 34, the pumping actuating member 2320 seals and accommodates the elastic pumping membrane 2330 with respect to the diaphragm opening 2390. To assist in sealing, the pumping actuation member 2320 may have a shape that is complementary to the shape of the diaphragm opening 2390. For example, the pumping actuation member 2320 may be spherical or conical, and the diaphragm opening 2390 may be a cylindrical through hole. At this stage of the applied stroke, backflow from the pumping chamber 2350 is blocked. Continued movement of the pumping actuating member 2320 deforms the elastic pumping diaphragm 2340 to increase the pressure in the pumping chamber 2350 while continuing to seal the diaphragm opening 2390 against backflow from the pumping chamber 2350. If the pressure in the pumping chamber 2350 provides sufficient fluid pressure for the one-way valve 22, fluid flows from the pumping chamber 2350 to the pump outlet 2370. During the return stroke, the pumping actuation member 2320, the elastic pumping membrane 2330, and the elastic pumping diaphragm 2340 return to the relaxed position shown in FIG. During the return stroke, the internal pressure of the pumping chamber 2350 and collection chamber 2345 decreases, but assists in refilling the valve pump 2200 by inducing fluid flow from the fluid source to the pump inlet 2310 and to the channel 2360. To do.

  Referring now to FIG. 35, a schematic cross-sectional view of one embodiment of an elastic pumping diaphragm 2340 is shown. The diaphragm body 2515 may be made of an elastic material such as silicone rubber. Further, elasticity may be applied to the flexible or already elastic main body 2515 including the diaphragm spring 2510. Diaphragm spring 2510 may be incorporated within elastic pumping diaphragm 2340 or may be disposed adjacent to elastic pumping diaphragm 2340. An example of one embodiment of diaphragm spring 2510 is shown in FIG. A combination of a diaphragm body 2515 that includes a flexible material and a diaphragm spring 2510 that includes an elastic material may be used. As a result, the pumping diaphragm 2340 exhibits a high degree of sealing and has a high degree of elasticity when contracted with an elastic pumping membrane 2330 deformed by a pumping actuating member (not shown, see FIGS. 32-34). The valve seat 2517 may be positioned around the diaphragm opening 2390. The valve seat 2517 may function as a receptacle for a deformed portion of the elastic pumping membrane 2330. The force applying member 2320 may deform the membrane 2330 by deforming the pumping membrane 2330, seal it and contact the valve seat 2517. When sufficient force is applied, the valve seat can be elastically deformed to ensure a complete seal against fluid backflow. The ratio of the cross-sectional height to the cross-sectional width of the valve seat 2517 can generally be selected differently and adapted to the flow environment.

  36, an embodiment of a diaphragm spring 2510 for use in the pumping diaphragm 2340 of FIG. 35 is shown. The outer annular portion 2520 and the inner annular portion 2540 are connected by at least three elastic arms 2530. The center of the inner annulus 2540 has a spring opening 2550 and can be aligned with the diaphragm opening 2390 of the pumping diaphragm 2340 as shown in FIG.

  Referring now to FIG. 37, a schematic diagram representing a cross-sectional view of the valve pump 2200 shown in FIGS. 32-34 above in combination with a force application assembly including a pumping actuation member 2320, an actuator, and a lever 273. Indicated. When excited by an actuator, such as shape memory actuator 278, lever 273 pivots about fulcrum 274 and initiates a compression stroke. The hammer 2630 protrudes from the lever 273. During the compression stroke, the hammer 2630 contacts the circular pumping actuating member 2320 and causes the pumping actuating member to move within the gap of the support structure 2660 such that the pumping actuating member 2320 is located within the elastic pumping diaphragm 2340. The pumping actuating member 2320 is pushed against the elastic pumping membrane 2330 until it is hermetically sealed. As the lever 273 continues to move, the pumping actuation member 2320 causes the pumping diaphragm 2340 to deform. When sufficient fluid pressure is applied to the one-way valve 22, the one-way valve 22 opens. This causes fluid to flow from pumping chamber 2350 to pump outlet 2370. In response to cooling of the shape memory actuator 278, the lever 273 is returned to the start position determined by the lever stop 2650 and the lever pawl 2640 by the elasticity of the pumping diaphragm 2340 and the elastic pumping film 2330. Alternatively, a return spring (not shown) may be used to return lever 273 to the starting position. Although shown as a sphere, the force member 2320 may alternatively be a piston, a protrusion on the lever 273, or other suitable form.

  FIG. 38 schematically shows a cross-sectional view of an embodiment of a valve pump using an elastic cylindrical curve 2670. In one embodiment, the elastic cylindrical curve is made of rubber, but in other embodiments it can be made of any elastic material. The cylindrical curved portion 2670 includes a central passage 2675 and a plurality of elastic radial fins 2672 that are hermetically arranged with respect to the housing 2673. Fluid entering the pump inlet 2310 passes through the channel 2360 and collects in the upstream region of the one-way valve 22 (collection chamber 2345, central passage 2675 of the cylindrical bend 2670, and pumping chamber 2350). The pumping chamber is connected in fluid communication with the collection chamber 2345 through a central passage 2675. During the compression stroke of the pumping mechanism, the pumping actuation member 2320 applies a force to the elastic pumping membrane 2330 to deform until the elastic pumping membrane 2330 is hermetically held against the valve seat 2680 of the cylindrical curved portion 2670. . Thereby, the back flow from the collection chamber 2345 to the pump inlet 2310 is blocked. Due to the continuous movement of the pumping operation member 2320, the cylindrical curved portion 2670 is deformed. Until sufficient time to open the one-way valve 22, the pressure in the pumping chamber 2350 increases. The fluid can then flow to the pump outlet 2370.

  The pumping actuation member 2320 is shown as a ball shape in FIG. However, in other embodiments, the pumping actuation member 2320 can be any shape that can function as described above.

  Referring now to FIG. 39, an alternative embodiment of a cylindrical curved portion 2670 (shown in FIG. 38) employing an elastic portion 2680 and a rigid cylindrical support 2690 is shown. Like the cylindrical curved portion 2680 of FIG. 38, the elastic portion of the cylindrical curved portion 2670 includes a valve seat 2680 that seals the central passage 2675 in response to application of force by the pumping actuation member 2320. Accordingly, the elastic portion 2680 of the cylindrical curved portion 2670 is deformed and transmits pressure to the pumping chamber 2350.

  Figures 40-44 schematically show cross-sectional views of alternative embodiments of the valve pump in various operating conditions. The valve pump 2200 of FIGS. 40 to 44 includes an elastic diaphragm spring 6100 and an elastic sealing film 6120, and performs a function similar to the elastic pumping diaphragm 2340 of the valve pump 2200 shown in FIGS. FIG. 40 shows the valve pump 2200 in a stationary state. At rest, fluid can flow from the inlet 2360 to the upper portion 2346 of the collection chamber 2345 and from the opening 6110 in the diaphragm spring 6100 to the lower portion 2347 of the collection chamber 2345. The fluid may then travel from one or more openings 6130 in the sealing membrane 6120 into the pumping chamber 2350. Under low pressure conditions, further fluid flow is blocked by the one-way valve 22. Both the spring diaphragm 6100 and the sealing membrane 6120 may be constructed from an elastic biocompatible material. The spring diaphragm 6100 may have a larger elastic force than the sealing film 6120. For example, the spring diaphragm 6100 may be a circular piece of flexible bioinert plastic and the sealing membrane 6120 may be a sheet of silicone or fluorinated silicone elastomer.

  41 and 42 show two intermediate, partially activated valve pumps 2200. FIG. The pumping actuating member 2320 deforms the pumping membrane 2330 and biases the spring diaphragm 6100 through the collection chamber 2345, thereby deforming and biasing against the sealing membrane 6120. At this point in the compression stroke, backflow to the opening 6110 of the spring diaphragm 6100 and / or the opening 6130 in the sealing membrane 6120 is inhibited. By an offset arrangement of the sealing membrane opening 6130 with respect to the spring opening 6100, a seal is created between the spring diaphragm 6100 and the sealing membrane 6120. In some embodiments, this seal may be supplemented by an excess seal between the fill chamber elastic pumping membrane 2330 and the spring diaphragm 6100 (eg, the embodiment of FIGS. 43-44, this excess seal is Absent). An outer peripheral portion (not shown) around the spring diaphragm opening 6110 may act as a valve seat to improve the sealing performance.

  42, the continued movement of the pumping actuation member 2320 causes further deformation of the pumping membrane 2330, the spring diaphragm 6100, and the sealing membrane 6120. As a result, the fluid in the pumping chamber 2350 is compressed until the fluid pressure opens the one-way valve 22. With further compression, the fluid flows out to the outlet 2370.

  An alternative embodiment of the valve pump 2200 of FIGS. 40-42 is shown schematically in FIG. In this embodiment, the pumping actuation member 2320 traverses the elastic pumping membrane 2330. The pumping membrane 2330 is hermetically attached to the outer periphery of the pumping operation member 2320 at an intermediate point along the length of the pumping operation member 2320. In operation, the diaphragm spring opening 6110 is sealed against reverse flow only by the sealing membrane 6120. The elastic pumping membrane 2330 does not contact the opening 6110. An alternative embodiment of the apparatus shown in FIG. 40 is shown in FIG.

  Referring now to FIG. 45, a cross-sectional view of an alternate embodiment of the combined valve pump 2200 is shown. The shape memory actuator 278 activates the compression stroke, thereby causing the elastic pump blade 2710 to move with a lever about the fulcrum 274 to deform the elastic pumping membrane 2330. The elastic pump blades 2710 and the elastic pumping membrane 2330 apply pressure to the fluid in the inclined pumping chamber 2720 having the shallow region 2730 and the deep region 2740. In the first half of the compression stroke, the pump vane 2710 causes the elastic pumping membrane 2330 to block the channel 2360 connecting the pump inlet 2310 and the inclined pumping chamber 2720. As the compression stroke continues, force is applied to the fluid in the inclined pumping chamber 2720 until the fluid pressure in the inclined pumping chamber 2720 is sufficient to open the one-way valve 22. The fluid then flows out from the pump outlet 2370. The pump blade 2710 may be wholly or partially composed of an elastic material such as rubber. In some embodiments, the elastic material includes inelastic splines. Alternatively, in some embodiments, the elastic force is applied through elastic region 2750, and thus elastic region 2750 is the only elastic component of pump vane 2710 in these embodiments. In these embodiments, the elastic region 2750 contacts the bottom of the inclined pumping chamber 2720. Due to the elasticity of the pump vane 2710, the pumping vane 2710 continues the compression stroke after contacting the base 2780 of the shallow region 2730. A return spring (not shown) returns the pump vane 2710 to the starting position during the return stroke.

  Referring now to FIG. 46, a cross-sectional view of an alternative embodiment of the pumping mechanism is shown. This embodiment includes elastic pump blades 2710. The elastic pump vane 2710 includes an elastic region 2830 that provides elastic force to the pump vane 2710. The elastic region 2830 joins the pumping actuation member 2820 to the pump blade 2810. When used with a valve pump (not shown), the elastic pump vane 2710 of FIG. 42 occludes the inlet channel (not shown, shown as 2360 in FIG. 45) and then bends in the flexible region 2830. The force member 2820 then applies additional pressure to the fluid in the inclined pumping chamber (not shown, shown as 2720 in FIG. 45). The force applying member 2820 may be entirely configured from an elastic material such as rubber. However, in an alternative embodiment, only the area in contact with the bottom of the pumping chamber (not shown) consists of an elastic material. The elastic pump blade 2710 returns to its relaxed structure during the return stroke.

  Referring now to FIG. 47, a cross-sectional view of another embodiment of the pumping mechanism is shown. A pumping mechanism is shown in which the lever is in an intermediate stage of operation with the inlet valve 2941 closed. The pumping mechanism includes a fluid line 2930, a movable member 2330, which in this embodiment is a membrane, an inlet valve 2941, a poppet 2940, a pumping actuation member 2942, a pumping chamber 2350, and an outlet valve 22. The inlet valve 2941 and the pumping actuating member 2942 are each operated by a shape memory actuator 278 that is provided around the return spring 276 and connected to the lever 273. The lever 273 operates both the inlet valve 2941 and the pumping operation member 2942. The lever 273 includes an elongated spring member 2910 attached to the lever 273 that is hinged to the fulcrum 274 and terminates in a valve operating hammer 2946. The spring member 2910 may be curved. Spring member 2910 biases valve actuation hammer 2946 away from lever 273 and biases to inlet valve 2941. The lever 273 has a pump actuation hammer 2948 that is not attached to the spring member 2910 and is positioned adjacent to the pumping actuation member 2942.

  The current causes the shape memory actuator 278 to contract and the lever 273 pivots around the fulcrum 274. The pivot step places valve actuation hammer 2946 in place and closes inlet valve 2941. As shape memory actuator 278 continues to contract, lever 273 continues to pivot and pump actuation hammer 2948 biases pumping actuation member 2942 against pumping chamber 2350 while elongate spring member 2910 is further compressed. To do. When sufficient pressure is reached, fluid pressure opens the outlet valve 22 and fluid flows out to the valve.

  During the relaxation stroke, the return spring 276 is unloaded, returning the lever 273 to the starting position and releasing the pumping actuating member 2942. The inlet valve 2941 is opened. The elasticity of the pumping chamber 2350 replenishes the pumping chamber 2350.

  48 and 49, a cross-section of an embodiment in which the pumping mechanism employs a bell crank 7200 and combines the valve pump 2200 and the flow bias valve is shown schematically. The bell crank 7200 converts the force generated by the linear shape memory actuator 278 into a lateral pumping force. FIG. 48 shows the mechanism in stationary or replenishment mode, and FIG. 49 shows the mechanism in the activated state. The contraction of the actuator 278 causes the bell crank 7200 to rotate around the shaft 7210 and press against the force member 2320, sealing the elastic membrane 7220 against the elastic pumping diaphragm 2340, allowing fluid to flow from the pumping chamber 2350 to the dispensing chamber 122. Energize. The return spring 276 cooperates with the return spring support 7221 to release the pumping force, expand the pumping chamber 2350 and draw fluid from the reservoir 20. 48 and 49, a flow bias valve 4000 having a valve spring 4010 and a poppet or plunger 4020 is also shown.

  In some embodiments of the pumping mechanism described above, one or more aspects of the following valve operation descriptions are relevant. Referring now to FIG. 50, an example of a closed flow bias valve 4000 is shown. The valve spring 4010 applies force to the poppet 4020 and seals and presses the valve membrane 4060 against the valve seat 4070 surrounding the terminal opening of the valve discharge port 4040. The valve seat 4070 may include a protruding portion in the circumferential direction to improve sealing. As described below with reference to FIGS. 54-55, the back pressure generated by the action of the elastic dispensing assembly should be insufficient to cause a back flow into the flow bias valve 4000. As shown in FIG. 51, when the pumping assembly is actuated, sufficient pressure is generated from the valve seat 4070 to disengage the membrane 4060 and the poppet 4020, thereby causing the inlet chamber from the valve inlet 4030 to enter the inlet chamber. Fluid flows through 4050 to valve outlet 4040. 52-53 show an alternative valve having a valve seat 4070 with no protrusions in the circumferential direction.

  54 and 55, there is shown a diagram of how an exemplary flow bias valve sorts forward and reverse flow. FIG. 54 schematically represents the valve in the closed position. The back pressure in the outlet 4040 exerts a force on a relatively small area of the flexible valve membrane 4060 adjacent to the valve seat 4070 and therefore cannot remove the poppet 4020. Referring now to FIG. 55, this diagram schematically represents the valve during actuation of the pumping actuation member. The pressure of the pumped fluid exerts a force on the membrane 4060 in a wider area than the area adjacent to the valve seat. As a result, the inlet pressure has a greater mechanical advantage for disengaging the poppet 4020, with forward flow depending on the action of the pumping actuating member. Therefore, the critical pressure required to displace the poppet 4020 is lower at the inlet than at the outlet. Thus, the spring bias force and force area size associated with both the fluid inlet and the fluid outlet can be selected such that the flow is substantially forward.

  Referring now to FIG. 56, similar to the flow bias valve of FIG. 50, it operates on the main structure, but requires the pressure required to open the valve, or “cracking pressure” (in some embodiments). , 0.2 to 20 pounds per square inch or “psi” can be adjusted). A cross-sectional view of adjustable flow bias valve 4130 is shown. The cracking pressure is adjusted by rotating the spring tension screw 4090 to change the volume of the recess 4080 and compress or restore the valve spring 4010, thereby changing the biasing force of the spring 4010. The valve spring 4010 biases the plunger 4100 against the valve membrane 4060 and biases it against the valve seat. Plunger 4100 serves as a force function similar to the fixed pressure poppet of the flow bias valve (shown as 4020 and 4000 in FIGS. 50-53, respectively). Compressing the valve spring 4010 reduces its biasing force, thereby increasing the cracking pressure. Conversely, restoring the spring 4010 reduces its biasing force and the associated cracking pressure. The valve spring 4010 is positioned coaxially around the shaft of the plunger 4100 and applies a biasing force to the plunger 4100. In some embodiments, the shaft of the plunger 4100 is shorter than the length of both the valve spring 4010 and the recess 4080 and may be freely displaced in response to increased fluid pressure in the fluid inlet 4030. Plunger 4100 may be any size necessary to function as desired. As in the embodiment of FIGS. 50-53, the wetted parts are present in the disposable portion 2610 and the force components (eg, plungers and springs) are present in the reusable portion 2620. Also good. The main structure of the operation is also similar. The greater mechanical advantage of the fluid inlet 4030 relative to the outlet 4040 favors forward flow as opposed to reverse flow. Alternatively, the plunger 4100 may be replaced with a poppet (shown as 4020 in FIGS. 50-55). In some embodiments, it may be desirable to eliminate the raised valve seat. In these embodiments, the plunger may be in the shape of a ball or another shape capable of concentrating forces.

  Flow bias valve 4000 substantially reduces or prevents backflow from dispense chamber 122 to pumping chamber 2350. 50-56, the valve spring 4010 biases the poppet or plunger 4040 and presses the membrane 7220 against the valve seat 4070 to provide a mechanical advantage for the forward flow through the line 310. By performing the functions of pumping membrane 2330 and valve membrane, membrane 7220 causes line 310, pumping chamber 2350, and pumping diaphragm 2340 to be placed in one component (e.g., disposable portion 2610) while the rest of the pumping mechanism is Can be present in two removable components (eg, reusable portion 2620). By placing more durable and expensive components in the reusable portion 2620, economy and convenience can be realized.

  The pumping mechanism described in the various embodiments above can be used in various devices to pump fluid. As an exemplary embodiment, the pumping mechanism described in FIGS. 59A-59E, 60A-60D, and 60A-60C is described as being integrated into a fluid pumping device.

  Referring to FIGS. 57 and 58, an alternative method of fluid schematic is shown. These are two schematic views of the reservoir 20 and pumping assembly 16 being coupled to the dispensing assembly 120. In the embodiment shown in FIG. 57, the reservoir and pumping assembly are coupled in parallel to the dispensing assembly 120. In the embodiment shown in FIG. 58, the shunt line 150 is connected back from the output of the pumping assembly 16 to the reservoir 20. Since much of the fluid output of the pumping assembly 16 returns to the reservoir 20 via the shunt line 150, the pumping assembly 16 may not function as desired in the embodiment shown in FIG. Can be accommodated. Thus, in some embodiments where a large volume pumping mechanism is employed, the shunt line 150 can provide a small volume function for the large volume pumping mechanism. One-way valves 21 and 22 are oriented in the same direction and are included to prevent unwanted backflow.

  Referring now to FIG. 59A, a fluid schematic diagram of one embodiment of a fluid pumping device is shown. In this embodiment, the fluid is located in the reservoir 20 connected to the fluid line 310. The fluid line 310 communicates with the pumping mechanism 16 separated by the membrane 2356. Fluid is pumped from the flow restrictor 340 to an infusion device or patient cannula 5010. It should be understood that the infusion device or cannula 5010 is not part of the device, but is attached to the patient for fluid delivery. System embodiments are described in detail below, which include an infusion device or cannula 5010.

  Referring now to FIG. 59B, an alternative embodiment of the schematic shown in FIG. 59A is shown. In the embodiment shown in FIG. 59A, fluid is pumped to flow restrictor 340 and then to cannula 5010. However, in FIG. 59B, fluid is not pumped to the flow restrictor. Conversely, the fluid has the same impedance and is pumped into the cannula 5010.

  In both FIGS. 59A and 59B, a constant volume of fluid is pumped into the patient, and in one embodiment approximated by the pump stroke. The stroke length provides an estimate of the volume pumped to the patient.

  Referring now to FIG. 59C, a fluid schematic diagram of one embodiment of a fluid pumping apparatus is shown. In this embodiment, the fluid is located in the reservoir 20 connected to the fluid line 310 by the diaphragm 6270. The fluid line 310 communicates with the pumping mechanism 16 separated by the membrane 2356. The fluid is pumped to the variable volume delivery chamber 122 and then from the flow restrictor 340 to the patient delivery cannula 5010.

  The volume of fluid delivered is determined using a dispense assembly 120 that includes an acoustic volume sensor (AVS) assembly (as described above), a variable volume delivery chamber 122, and a dispense spring 130. The Similar to the pumping mechanism, the membrane 2356 forms a variable volume dispensing chamber 122. The membrane is made of the same material (or, in some embodiments, a different material) as membrane 2356 in pumping mechanism 16 (detailed above). The AVS assembly is detailed above.

  Referring now to FIG. 59D, which is an alternative embodiment to the embodiment shown in FIG. 59C, in this embodiment there is no flow restrictor between the variable volume delivery chamber 122 and the cannula 5010. 59E, an alternative embodiment to the embodiment shown in FIG. 59C is shown with an alternative pumping mechanism 16.

  Referring now to FIGS. 59A-59E, the reservoir 20 can be any fluid source and can safely hold a syringe, collapsible reservoir bag, glass bottle, glass vial, or fluid to be delivered. Including, but not limited to, any other container. The diaphragm 6270 is the connection point between the fluid line 310 and the reservoir 20. Various embodiments of the diaphragm 6270 and the reservoir 20 are described in detail below.

  The embodiment of the fluid delivery device shown in FIGS. 59A-59E can be used for the delivery of any type of fluid. Furthermore, this embodiment can be used as one, two, or three separate mating parts. 60A-60D, the same embodiment described with reference to FIGS. 59A-59D is shown separated into mating parts. Part X includes a moving part, and part Y includes a fluid line 310 and a membrane 2356. In some embodiments of the design, part Y is a disposable part and part X is a non-disposable part. The part X is not in direct contact with the fluid, and the part Y is a part having only a liquid contact region. In the embodiments described above, the reservoir 20 can be of any size and is integrated into either the present disposable part or a separate disposable part. In any embodiment, the reservoir 20 can be refillable. In embodiments where the reservoir 20 is integrated into the disposable part Y, the reservoir 20 is manufactured to be filled with fluid or the patient or user can use the syringe to remove the reservoir 20 through the septum 6270. Fill. In embodiments where the reservoir 20 is a separate mating component, the reservoir 20 is manufactured to be filled with fluid, or the patient or user uses a syringe (not shown) to create a reservoir loading device. Reservoir 20 is filled through diaphragm 6270 as part of (not shown, detailed below) or manually using a syringe. Further details regarding the process of filling the reservoir 20 are described below.

  While various embodiments have been described with respect to FIGS. 59A-59E and FIGS. 60A-60D, the pumping mechanism is any pumping mechanism described in the embodiments herein or alternative embodiments having similar functions and features. It is possible that there is. For example, referring to FIG. 61A, a similar embodiment as shown in FIG. 59A is shown having an exemplary block that includes a pumping mechanism 16. This indicates that any pumping mechanism 16 described and functioning similarly can be used in the fluid pumping device. Similarly, FIGS. 61B and 61C are depictions of systems that include the embodiments of FIGS. 59B and 59C, respectively.

  The schematic diagram of the fluid pumping device described above can be implemented in a device that can be used by a patient. There are several embodiments. The device can be integrated into a stand-alone device or another device. The device can be any size or shape. The device can be either portable or non-portable. The term “portable” means that the patient can be carried in the pocket, worn on the body, or otherwise carried the device. The term “non-portable” means that the device is in a medical facility or home, but the patient does not carry the device to almost any place where it moves. The remainder of this description concentrates on the portable device as an exemplary embodiment.

  Because it is a portable device, the device can be worn by the patient or carried by the patient. In embodiments where the device is worn by a patient, it is referred to as a “patch pump” for purposes of this description. When a patient carries the device, it is referred to as a “portable pump” for purposes of this description.

  The following description applies to various embodiments for either the patch pump embodiment or the portable pump embodiment. In various embodiments, the apparatus includes a housing, a pumping mechanism, a fluid line, a movable member, a reservoir, a power source, and a microprocessor. In various embodiments, a dispensing assembly, eg, a volume sensing device (including an AVS assembly in some embodiments) is included in the device. Certain embodiments may also include a fluid restrictor, but are not described in the following figures, and the fluid lines are shown homogeneously to simplify the figures. For purposes of this description involving a dispensing assembly, an exemplary embodiment includes an AVS assembly. An AVS assembly is the preferred embodiment, although other types of volume sensing devices can be used in other embodiments. However, in some embodiments, no volume sensing device is used, and conversely, the reservoir itself determines the volume of fluid delivered or uses a pump stroke to approximate the volume delivered. It should be understood that the schematic apparatus shown herein is intended to illustrate some variations within the apparatus. Also, the embodiments represented by these schematic views each include a sensor housing, a vibration motor, an antenna, a wireless communicator, or other components described with reference to FIGS. 70-70D. Is possible. Accordingly, these depictions are not intended to limit the components, but conversely, to illustrate how the various components can be correlated within the device.

  Referring now to FIG. 62A, a schematic diagram of the stand-alone device 10 is shown. The housing 10 has an arbitrary shape or size and can accommodate a target application. For example, if the device is used as a patch, the device is sufficiently compact to be so worn. When the device is used as a portable pump, the device is sufficiently compact to be used as such. In some embodiments, the housing is made of plastic, and in some embodiments, the plastic is any injection-molded fluid compatible plastic such as, for example, polycarbonate. In other embodiments, the housing consists of a combination of aluminum or titanium and plastic or any other material, and in some embodiments the material is lightweight and durable. Additional materials can include, but are not limited to, rubber, steel, titanium, and alloys thereof. As shown in FIG. 62A, the device 10 can be any desired size or shape.

  62A-69B are schematic diagrams illustrating an exemplary embodiment. The exact design will depend on many factors, including but not limited to the size of the device, power limitations, and the intended application. 62A-69B are therefore intended to illustrate various features and possible combinations of devices, however, actual devices can be readily designed and implemented by those skilled in the art. As an example, an apparatus embodiment is described and illustrated below. However, these are not intended to be limiting and, conversely, are intended to be examples.

  Next, referring to FIG. 62B, for some patch devices, the housing 10 includes an insertion region confirmation window 342 for some embodiments. This allows the location of the patient to be inserted with an infusion device or cannula (not shown). Shown here is the cannula housing 5030 region of the device 10. The confirmation window 342 is made of any material that is transmissive, including but not limited to plastic. Although the confirmation window 342 is shown as being at one particular position on one particular shape device, the confirmation window 342 can be integrated at any desired position within any housing embodiment.

  Referring now to FIG. 63A, the apparatus 10 is shown. Reservoir 20 is shown connected to fluid line 310 (and then connected to pumping mechanism 16). Dispensing assembly 120 is shown connected to fluid line 310. Pumping mechanism 16 and dispensing assembly 120 are separated from fluid line 310 by membrane 2356. Cannula housing 5030 is downstream from the volumetric device. Shape memory actuator 278 is shown connected to pumping mechanism 16. A microprocessor on the printed circuit board 13 and a power supply or battery 15 are included. Also, a flow impedance as described above can be implemented between the dispensing assembly 120 and the cannula housing 5030.

  Referring now to FIG. 63B, the present embodiment shows a similar device 10 as shown in FIG. 63A, except that the dispensing assembly is not included. In this embodiment, the delivered fluid volume is either pump stroke (number and length), reservoir 20 (volume and time), or both, or any other described above for monitoring the delivered fluid volume. Depends on the method.

  Referring now to FIG. 63C, a similar device 10 as shown in FIG. 63B is shown except that the device 10 includes a dispensing chamber 122 and a sensor housing 5022.

  Referring now to FIG. 64A, one embodiment of the patch pump device 10 is shown. This embodiment is based on the embodiment of apparatus 10 shown in FIG. 63A. In this embodiment, the patch pump device 10 is divided into two sections (upper X and base Y). The top X includes a pumping mechanism 16, a dispensing assembly 120 (optional but shown as an exemplary embodiment), a power supply 15, and a microprocessor and printed circuit board 13. They are not in direct contact with non-wetted elements, i.e. fluid. Base Y includes fluid line 310 and membrane 2356. In addition, when the reservoir 20 is built in the apparatus, the reservoir is also included in the base Y. However, in embodiments where the reservoir 20 is a separate mating part, the reservoir 20 is connected to the fluid line when fully assembled (see FIGS. 66A-66D and description thereof), however, the apparatus Is not built in.

  The patch pump device also includes a cannula housing 5030. This is the area where the cannula line 5031 is located. By means of a cannula line 5031, which is part of the fluid line 310, the cannula (or other infusion device) receives the fluid and delivers it to the patient (not shown).

  Referring now to FIG. 65A, in some embodiments, the cannula 5010 is inserted through the housing 5030 directly into the patient. Cannula 5010 is connected to a septum (not shown) that connects cannula line 5031 to cannula 5010. Referring now to FIG. 65B, in another embodiment, an insertion set (including a cannula and a tube, not shown in FIG. 65B, but shown as elements 5033 and 5010 in FIG. 64B) is used. Accordingly, the insertion set tube 5033 is connected to a cannula line 5030 at one end of the tube and a cannula (not shown) at the other end.

  Referring again to FIG. 64A, in use, a reservoir 20 containing fluid therein (formed into the base Y or separately attached to the base Y as described above) is connected to the fluid line 310. Is done. The microprocessor on the printed circuit board 13 sends a signal, activates the pumping mechanism 16, and a stroke is initiated through the current applied to the shape memory actuator 278. Fluid flows from reservoir 20 through fluid line 310 to dispense assembly 120 or AVS assembly. Here, the exact fluid volume in the AVS chamber is determined and fluid is forced from the AVS chamber to the cannula line 5031 and cannula housing 5030.

  Referring now to FIG. 64B, the device shown in FIG. 64A is shown connected to an insertion set, a tube 5033, and a cannula 5010. In FIG. 64C, the base Y of the device is shown using an adhesive patch or pad 3100 on the patient 12 body. Note that in this embodiment, element 3100 can be either a pad or a patch. However, as detailed below, element 3100 is referred to as a patch and element 3220 is referred to as a pad. Element 3100 is used for simplification purposes only. However, in some embodiments, a pad is used, and thus element 3220 is appropriate in those situations.

  A cannula 5050 is inserted into the patient 12 by means of a cannula septum 5060 that is inserted through the cannula housing 5030 to fit into the cannula line 5031. However, as shown and described above with respect to FIG. 2B, the base Y can be fluidly attached to the patient through an insertion set that includes a tube 5033 and a cannula 5010. In both FIGS. 64B and 64C, the base Y can be adhered to the patient before or after insertion of the cannula 5010. Referring again to FIG. 2C, when cannula 5010 is inserted into patient 12, it receives fluid directly from the device without using an infusion set tube (shown in FIG. 64B). The base Y can be adhered to the patient by an adhesive patch 3100 before or after insertion of the cannula 5010. Referring now to FIG. 64D, the top X of the device 10 is attached to the base Y of the device 10 after the cannula 5010 has been inserted into the patient 12.

  As described below, the adhesive patch can have many embodiments, and in some cases, the patch is placed on top of the device. Accordingly, the patches shown in these embodiments are only one embodiment. As described above, the pad (if used) is placed at the same position as the patches of FIGS.

  66A-66D, in this embodiment, the reservoir 20 is shown as a separate part. As shown in FIG. 66A, the base Y includes a reservoir cavity 2645 with a diaphragm needle 6272. As shown in FIG. 66B, the reservoir 20 is initially placed in the upper reservoir cavity 2640. At this point, the reservoir 20 is not attached to the apparatus. Next, referring to FIG. 66C, when the top X is placed on the base Y, the reservoir 20 is clamped within the base reservoir cavity 2645. As shown in FIG. 66D, the force generated by the attachment of the top and base Y pushes the diaphragm needle 6272 into the diaphragm 6270 of the reservoir 20 connecting the reservoir 20 to the fluid line 310 of the base Y.

  Referring now to FIGS. 67A-F, an alternate embodiment of the embodiment shown in FIGS. 64A, 64C and 66A-66D is shown. In these alternative embodiments, in addition to the cannula housing 5030, the base Y includes a sensor housing 5022. Referring now to FIGS. 69A-69B, both sensor housing 5022 and cannula housing 5030 include outlets to the bottom surface of base Y, shown as 5022 and 5030, respectively, in FIG. 69A. FIG. 69B shows the embodiment shown in FIG. 69A with a sharpened portion protruding through the housing. The sensor housing accommodates the sensor. In some embodiments, the sensor is an analyte sensor. The analyte to be sensed includes blood glucose, but in other embodiments, the analyte sensor can be any type of analyte sensor desired.

  Referring now to FIG. 67B, the base Y is shown on the patient 12 body. Sensor 5020 is shown inserted into patient 12 through base Y sensor housing 5022. Referring now to FIG. 67C, in some embodiments, cannula 5010 and sensor 5020 are simultaneously inserted into patient 12 through their respective housings (5030 and 5022). Referring now to FIG. 67D, base Y is shown attached to a patient having both cannula 5010 and sensor 5020 attached to patient 12 through base Y.

  Referring now to FIG. 67E, base Y is attached to patient 12 and cannula 5010 is shown inserted through cannula housing 5030. In this embodiment, the sensor housing 5022 is shown without a sensor. However, sensor 5020 is shown inserted at another location on patient 12. Thus, the sensor 5020 need not be inserted through the base Y, but the embodiments described below for monitoring blood glucose and pumping insulin through the cannula can be implemented in this way. is there. Furthermore, other embodiments relating to administering a fluid, depending on or in connection with the analyte level, can be administered in the present method.

  Referring now to FIG. 67F, device 10 having both sensor 5020 and cannula 5010 through base Y is shown with top X mounted thereon. Again, in the embodiment shown in FIGS. 66A-66D, when the top X is mounted on the base Y, the reservoir 20 fluidly connects with the fluid line 310.

  Referring now to FIG. 68, one embodiment of the portable pump embodiment of the device 10 is shown. In the device 10, an insertion set including a cannula 5010 and a tube 5033 is required to connect a fluid line in the device 10 to the patient 12. Thus, in this embodiment, the cannula 5010 is not directly connected to the patient 12 from the portable pump device 10. Further, although this embodiment can function for analyte sensors and fluid pumps as described below, the sensor 5020 is external to the portable pump device 10 similar to the embodiment of the sensor 5020 shown in FIG. 5F. Be positioned.

  Referring now to FIGS. 70-70D, both the patch pump and portable pump embodiments as described include the various components of the embodiment including the dispensing assembly (in the applicable embodiment) and the AVS assembly. In addition, the various components include at least one microphone, a temperature sensor, at least one speaker, a variable volume dispensing chamber, a variable volume chamber, a port, and a reference chamber. In some embodiments, the apparatus includes one or more of the following. A vibration motor (and, in those embodiments, a motor drive), an antenna, a wireless communicator, a skin temperature sensor, a bolus button, and in some embodiments, one or more additional buttons. In some embodiments, the antenna is a quarter wave tracking antenna. In other embodiments, the antenna may be a half-wave or quarter-wave tracking, dipole, monopole, or loop antenna. The wireless communicator is 2.4 GHz in some embodiments, but in other embodiments has a frequency of 400 MHz. In still other embodiments, the wireless communicator can be at any frequency. Thus, in some embodiments, the device includes a wireless communicator that is sufficiently strong to communicate with the receiver within a few feet of the device. In some embodiments, the apparatus includes a second wireless communicator. In some embodiments, the second wireless communicator may be a specific long range frequency, eg, 433 or 900 MHz, or in some embodiments any frequency within the ISM band or other band. Good. Although not shown in FIGS. 70-70D, the apparatus includes a screen and / or user interface in some embodiments.

  The following description of these components and their various embodiments applies to both the device types and the various embodiments described with respect to each device type. Referring now to FIG. 67F, both cannula 5010 and sensor 5020 have been inserted into device 10 for illustration purposes only. Referring also to FIGS. 70-70D, various components (some are not necessarily included in all embodiments) are shown in a schematic diagram representing the electrical connections of those components. Accordingly, FIGS. 70-70D represent various elements that may be included in the apparatus. These can be mixed and adapted depending on size requirements, power limitations, applications, and preferences, as well as other variables. FIG. 70 shows the relationship of FIGS.

  The apparatus includes at least one microprocessor 271. This can be at least a microprocessor of any speed capable of handling the various electrical connections necessary for the functioning of the device. In some embodiments, the device includes two or more microprocessors, and as can be seen in FIGS.

  The microprocessor 271 (or a plurality of microprocessors in some embodiments) is connected to a main printed circuit board (hereinafter, “PCB” indicates “printed circuit board”) 13. In some embodiments, a power source that is a battery 15 is connected to the main PCB 13. In one embodiment, battery 15 is a rechargeable lithium polymer battery. In other embodiments, the battery can be any type of replaceable or rechargeable battery.

  In some embodiments, the apparatus includes a wireless communicator 370 connected to the main PCB 13. Wireless communication device 370 communicates with remote control device 3470 using antenna 3580. Thus, communication between the device 10 and the remote control device 3470 is wireless.

  In some embodiments, the apparatus includes a vibration motor 3210. The vibration motor 3210 is connected to a motor drive device 3211 on the main PCB 13 motor drive device 3211.

  Some embodiments include a bolus button 3213. Bolus button 3213 functions by the user applying a force to button form 3213 (which can be made of rubber or any other suitable material). The force activates the bolus button operation (attached to the bolus button switch 3214 on the main PCB 13). Switch 3214 activates a single bolus indicating the specific predetermined fluid volume delivered to the patient. After the user presses the bolus button 3213, in some embodiments, the device 10 issues an alarm (eg, activates the vibration motor 3210 and / or sends a signal to the remote control device), and the button 3213 is A signal is sent to the user that the button has been pressed. The user then needs to confirm whether the bolus is to be delivered, for example, by pressing button 3213. In yet another embodiment, the remote control 3470 queries the user to see if a bolus is to be delivered.

  In various embodiments, a similar query / response order may be used to test and report patient responsiveness. For example, the device is configured to test patient responsiveness by issuing an alarm (eg, an audible and / or tactile alarm) and waiting for a response from the patient (eg, activation of button 3213). May be. Such tests are based on detection of conditions such as abnormal specimen levels monitored via various time periods (eg every 5 minutes) or via a specimen sensor, or abnormal body temperature monitored via a temperature sensor. , May be done. If the patient does not provide an appropriate response within a predetermined time, the reusable part may send an alarm to the remote control or caregiver. Such testing and reporting may be particularly beneficial for patients who may become unconscious or unable to respond to device malfunctions or otherwise.

  A NITINOL circuit (see shape memory actuator, in some embodiments, NITINOL fiber bundle) 278 on the main PCB 13 provides current to the NITINOL connector. As shown in FIG. 67F and FIG. 70A, the device can include two NITINOL connectors 278 (and two NITINOL fiber bundles). However, as described above, in some embodiments, the device includes one NITINOL connector (and one NITINOL fiber bundle).

  In some embodiments, the apparatus includes a temperature sensor 3216 shown in FIG. 70B. The temperature sensor 3216 is located on the bottom surface of the base Y and senses the patient's skin temperature. Skin temperature sensor 3216 is connected to a signal converter represented by 3217. As shown in FIG. 70B, the signal converter 3217 is represented as one block, however, the apparatus includes multiple signal converters that filter different signals as needed. Subsequently, the AVS temperature sensor 132, the AVS microphone 133, and the analyte sensor 5020 are all connected to a signal converter represented by 3217 as one block.

  The AVS speaker 134 is connected to the speaker driving unit 135 on the main PCB 13. The AVS speaker 134 is a hearing aid speaker in one embodiment. However, in other embodiments, the speaker 134 (speaker including a voice coil and a magnet having an electromagnet coil) is a piezoelectric speaker (shown in FIG. 50, representing one embodiment of the apparatus).

  Still referring to FIGS. 70-70D, in some embodiments, the antenna 3580 has a dedicated PCB 3581 (which is then connected to the main PCB 13). In some embodiments, the AVS microphone 133 includes dedicated PCBs 1332 and 1333 that are connected to the main PCB 13, respectively. The various PCBs may be connected to the main PCB 13 using conventional methods, for example, flexible circuits or wires.

  Referring to FIG. 67F, for purposes of explanation, the apparatus 10 is shown as an exemplary embodiment. However, the layout of the various components can be changed and many of the embodiments are described below. However, additional alternative embodiments are not shown, but can be determined based on size, power, and application.

  According to an alternative embodiment, the disposable portion 2610 may include the reservoir 20 and optionally a battery. Reservoir 20 may be integrated into the disposable part or otherwise coupled to the disposable part. The battery may be the primary or single power source of the device, or may be an auxiliary power source, and to provide power to electronics on reusable and / or disposable parts. May be used. Both the reservoir 20 and the battery typically require periodic replacement, so including both of these components in the disposable portion 2610 provides the user with the convenience of simultaneous replacement. Can be provided. Furthermore, by replacing the battery each time the reservoir is replaced, the user may be less likely to run out of battery.

  The disposable portion 2610 may additionally or alternatively be used in the event of a failure, for example to continue certain device operations in the event of a failure (eg, a failure of the main controller in the reusable portion). It can include a processor that can be used to raise an alarm or to provide status information to a reusable part. With respect to status information, the processor records the operating history and various characteristics of the disposable part, and the state of the user interface 14 including during user access, fluid delivery device 10, and / or installation of the disposable part 2610. It is possible to hold information. For example, the processor may store status regarding shelf life, maximum exposure or operating temperature, manufacturer, therapeutic drug safety restrictions, and the like. If any of these condition indicators are determined by the device to be unacceptable, the device will refuse to supply power to the pumping and dispensing assembly and the disposable part will be unusable. It is possible to indicate to the user that this is possible. The processor may be powered by a battery in a reusable or disposable part.

  More specifically, the device can be applied to any disposable part (eg, disposable), eg, from a processor located in the disposable part, via a barcode reader, or via RFID technology. Configured to obtain status information from portion 2610 and any disposable component used with it, such as a fluid reservoir, battery, or sharp cartridge, or individual sharp component. May be. If the device detects a problem with a disposable part (e.g., invalid model number for use with a reusable part, fluid expiration date), then the device may, for example, operate the device Corrective action may be taken, such as blocking or terminating and issuing an appropriate alarm.

  Additional components may be included in some embodiments. For example, it is possible to employ a surplus fault detection and warning mechanism. The device may employ an audible alarm. The loudspeaker 1202 of the sensor 550 may be used for an audible alarm, or an additional speaker may be included in the loudspeaker and used for an audible alarm. The device vibration mechanism 3210 can also be used as an alarm. Both alarms can be triggered if a system failure is detected that requires first aid. Further, a secondary battery or a super capacitor may be employed as an auxiliary to the primary battery. If any battery fails, the controller can trigger at least one alarm to generate at least one warning of battery failure.

  The alarm can also be used to indicate to the user that the device is operating properly. For example, the user may program the device for a period of bolus delivery. The user may wish to confirm that the programmed delivery is occurring properly. The processor can use a vibration motor or audible sound to indicate that the programmed delivery is good. Thus, several mechanisms can be employed in some embodiments of the device for providing to a patient or user, regardless of positive or negative feedback.

  A microphone may also be used to detect any abnormal vibration or lack of normal vibration and trigger an alarm condition. In various embodiments, an acoustic volume sensor system microphone may be used to perform such monitoring, or a separate microphone may be included for such monitoring. It is also possible to perform periodic checks to determine that the device is operating by using a microphone to check for expected pump vibrations. An alarm can be triggered if inappropriate vibration is detected, or if proper vibration is not detected by the microphone.

  Referring now to FIG. 71, various components of the device 10 are shown schematically. In one embodiment of the apparatus 10, the upper X portion fits with the base Y and the reservoir 20 is sandwiched between the upper X and the base Y. The reservoir diaphragm 6272 is fitted to the base Y by the clamping force. In some embodiments, both the infusion device 5010 and the analyte sensor 5020 are inserted through the base Y into a patient (not shown).

  In many embodiments, the base Y and reservoir 20 are disposable parts and the top X is a non-disposable part. Further, both the injection device 5010 and the analyte sensor are disposable.

  As noted above, the patch pump device may be wholly or partially disposable. FIG. 72 illustrates an embodiment of the fluid delivery device 10 having disposable and non-disposable parts. In this embodiment, the disposable portion Y includes a collapsible reservoir 20, a pumping assembly (not shown), a variable volume dispensing chamber 122 (part of the dispensing assembly 120, located at the top X), and a flow restriction. Components (not shown), as well as one-way valves (not shown), and components in direct contact with the fluid, such as a fluid path (not shown) connecting the reservoir from the pumping mechanism to the variable volume dispensing chamber 122 . Further, the disposable portion Y includes a reservoir cavity 2645.

  The reusable part X includes the elements of the dispensing assembly 120 except for the variable volume dispensing chamber 122 located in the disposable part Y. In some embodiments, dispensing assembly 120 is an AVS assembly. The AVS assembly is detailed above. Referring now to FIG. 73, an integrated acoustic volumetric sensor is shown on the PCB.

  Referring now to FIG. 74, the apparatus 10 shown in FIG. 49 is shown. The base disposable portion Y includes a reservoir cavity 2645. The upper non-disposable part X includes the battery 15 and the dispensing assembly 120. Microphone 133 is shown with diaphragm spring 130. In some embodiments, dispensing assembly 120 includes two or more microphones. Throughout this description, each microphone is referred to as 133, but does not imply that the microphones are always equivalent. In some embodiments, the microphone is the same, but in other embodiments, the microphone is different.

  In FIG. 74, the upper non-disposable part X includes the main PCB 13, the vibration motor 3210, and the pumping operation member 54. The upper non-disposable part X includes the AVS assembly or dispensing assembly 120. In FIG. 74, the microphone 133 is shown. The upper non-disposable part X also includes a battery 15 that can be used to provide power to the non-disposable part and / or the electronics on the disposable part. In some embodiments, the battery 15 is rechargeable. The step of charging can be performed by the method described below. The disposable part Y includes wetted components such as a fluid line (not shown) and a pumping assembly. In FIG. 74, only the pumping plunger 54 can be confirmed. Embodiments of the device 10 can also include many of the elements described above, including but not limited to fluid impedance, flexible membranes, cannula housings, and sensor housings. . Any pumping mechanism can be used.

  Referring now to FIG. 75, the device 10 is shown from another perspective where the elements are more visible. In FIG. 75, the device 10 is shown as a base disposable portion Y that includes a coiled tube flow restrictor 340 and a fluid line 310 connected to the inlet 21 and outlet 22 valves. A pumping actuation member 54 is also shown. The upper part X includes a main PCB 13, a vibration motor 3210, two microphones 133, a speaker 134, a reference chamber 127, and a fixed volume chamber 129. A battery 15 is also shown. When selecting a small diameter for the flow restrictor 340, it may be desirable to use a larger diameter, longer tube, as blockage of the line 310 may occur (eg, due to protein aggregation within the treatment fluid). is there. However, in order to wrap a longer tube in a patch-sized housing, it may be necessary to bend the tube into a serpentine path shape, such as a coiled or serpentine shape.

  Referring now to FIG. 76, an exploded view of the device 10 shown in FIGS. 72, 74 and 75 is shown. The upper non-disposable part X is shown separated from the base disposable part Y. In practice, a reservoir (not shown) is placed between the upper X and base Y portions. Once the top X and base Y are assembled and the device 10 is formed, the reservoir is connected to the fluid line 310.

  Referring now to FIG. 77, an exploded view of another embodiment of the device 10 is shown that includes a disposable base Y and a non-disposable top X part. Also included are a reservoir 20, an adhesive 3100, and a bridge 5040 instrument that holds the infusion device 5010 and sensor 5020. The device 10 includes a more circular footprint and dome shape. Battery 15 and main PCB 13 are shown located on top X. Base Y includes a reservoir cavity 2645. The adhesive 3100 is shown in two fragment embodiments. The bridge 5040 is shown with an irregular shape, although the reservoir 20 used to insert the infusion device 5010 and the sensor 5020 through the base Y is shown, however, in other embodiments, the reservoir 20 is optional. The size can be varied according to the desired fluid volume. In this embodiment of the device 10, the non-wetted component is in the upper non-disposable X and the wetted component is in the disposable portion Y of the base.

  During assembly, the device 10 may be glued together using a central area of adhesive (not shown). Alternatively, the device 10 may be mechanically locked together using any of the many embodiments described herein for latching. Although some embodiments are described later herein, many others are also apparent, and in many cases, the latches also change as the device changes shape.

  78, an exploded view of another embodiment of the device 10 is shown. The upper non-disposable portion X is most often dome-shaped, however, the protrusion X1 is shown to accommodate the mechanism within the upper X. Thus, the device shape can vary and includes polyps and protrusions, dimples, and other tissue-like properties to accommodate the various designs of the device.

  Reservoir 20, infusion device 5010, and sensor 5020 are shown. The infusion device 5010 and sensor 5020 can be inserted through the base Y into a patient (not shown). Base Y is shown with adhesive 3100 or pad 3220 at the bottom. In practice, the adhesive 3100 or pad 3220 can first be adhered to the skin and base Y. The infusion device 5010 and sensor 5020 are then inserted through the base Y into the patient (not shown, shown as 5020 and 5010 in FIG. 79). The reservoir 20 is then placed first on the top X and then either by sandwiching the top X and the base Y or by placing the reservoir 20 in the reservoir cavity 2645 and then the top X And the base Y are placed in the reservoir cavity 2645. Either method can be used. The final result is that reservoir 20 is connected to a fluid line (not shown) located at base Y through a diaphragm (shown upside down) and diaphragm needle (not shown, see 6272) on reservoir 20. Become. The top X is then secured to the base X using adhesive or, in this embodiment, mechanically using a latch 654 to bite the top X and base Y together.

  The base Y includes components to be wetted. The base Y is disposable. The top X contains non-wetted components. The top X is not disposable. Referring now to FIG. 79, the base Y includes a variable volume dispensing chamber 122, an inlet valve 21, an outlet valve 22, and a pumping chamber 2350. As shown in this figure, the elements are shown as a membrane over a region that acts as a chamber or valve. Thus, the base Y includes a membrane that maintains the wetted area firmly and thus maintains the non-wetted area as at the top (not shown). As shown in FIG. 79, the sensor 5020 and the infusion device 5010 are inserted into the respective housing and through the base Y to the patient (not shown). Although the base Y is shown with a reservoir cavity 2645, the reservoir (not shown) needs to be connected so that the fluid line from the reservoir to the chamber and to the infusion device is connected.

  Referring now to FIG. 80, the top X of the device is shown. Top X includes non-wetted components such as temperature sensor 3216, diaphragm spring 130, inlet valve poppet 21, outlet valve poppet 22, and pumping actuation member 54 as shown. The upper portion Y includes an undulating portion 2640 for accommodating a reservoir (not shown).

  Referring now to FIGS. 81A-81C, an order to illustrate the process of sandwiching the reservoir 20 between the top X and the base Y is shown. As seen in FIG. 81A, the top X, as well as the reservoir 20 outside the top X, is shown. The reservoir includes a diaphragm 6270. The upper part X includes a reservoir relief 2640. Next, as shown in FIG. 81B, the upper part is prepared to be sandwiched with the base Y. Next, referring to FIG. 81C, the reservoir 20 is placed inside the base Y with the diaphragm side down. The diaphragm connects to a diaphragm needle (not shown) with a cannula inside the base Y, and connects the reservoir to a fluid line (not shown). In an alternative embodiment, the reservoir may include a cannulated needle rather than a septum, and the fluid path may include a reservoir interface with the septum rather than a cannulated needle.

  Referring now to FIG. 82, the top X is shown with one embodiment of the disassembled pumping mechanism 16. The pumping mechanism 16 is fitted into the pumping mechanism housing 18 in the upper part X. The base Y is also shown with one part of a latch 654 that bites both the top X and base Y.

  Referring now to FIG. 83, the base Y is shown with the fluid path assembly 166 and the membrane 2356 is disassembled from the base Y. This illustrates that in some embodiments of the device, the fluid path assembly 166 is a separate piece that is inserted into the base Y and clamped by the membrane 2356. Also, as shown in this figure, the adhesive or pad 3100/3220 includes openings for infusion devices and sensors (not shown) in some embodiments. Referring now to FIG. 84, a bottom view of the base Y is shown. It is the bottom of the fluid path assembly 166.

  Referring now to FIGS. 85A and 85B, another embodiment of the device is shown. In this embodiment, the top X is also non-disposable and includes a bolus button 654. The reservoir 20 is shown in an exploded view, however, in one embodiment, the reservoir 20 is built into the base Y. In another embodiment, the reservoir 20 is removable and is placed in the reservoir cavity 2645 using a similar process described above with respect to another embodiment of the device.

  The base Y is disposable and includes the wetted parts of the device 10. Sensor 5020, cannula 5010, variable volume dispensing chamber 122, inlet valve region 21, outlet valve region 22, and pumping chamber 2350. The volumetric dispensing chamber, inlet valve region 21, outlet valve region 22, and pumping chamber 2354 are all covered by membrane material, which may be in the form of a single membrane or individual membranes.

  Device 10 is bitten together by a latch mechanism 654 on top X and base Y. Referring now to FIGS. 85C-85D, the device 10 is a latching mechanism 654 shown in an open position (FIG. 85C) and a bitten or closed position (FIG. 85D). As detailed above, a bolus button 3213 is also shown.

  A cover (not shown) may be provided for use in any of the embodiments of the device to replace the reservoir and top when the reservoir is removed when the base is connected to the patient. Good. The cover does not contain electrical components and can therefore be used even in wet conditions. However, in some examples, the reservoir can be removed without using any cover.

(Cannula and insertion device)
FIG. 86A schematically illustrates an exemplary embodiment of an infusion and sensor assembly 5040 that includes both an infusion device that can be a cannula or needle 5010 and an analyte sensor that includes a sensor probe 5025 and a sensor base 5023. The bridge 5070 firmly joins the infusion cannula 5010 and the analyte sensor base 5023. The infusion device 5010 is bounded on the upper side by a diaphragm 5060 that allows fluid to flow from the source and to be administered to the patient through the infusion device 5010. The sensor base 5023 is a section of the analyte sensor that is not inserted into the patient. In one embodiment, the base 5023 has electronic contacts for electrochemical analysis of blood glucose. The probe 5025 protrudes from the base 5023 of the analyte sensor 5020.

  Referring now to FIG. 86B, in this embodiment, the injection device 5010 is a cannula that is introduced into the patient using the patient introduction needle 5240. The introducer needle 5240 is inside the cannula 5010 when inserted into the patient. After insertion of the cannula 5010 into the patient, the introducer needle 5240 is removed and the septum 5060 is sealed against a fluid source (in some embodiments of the devices described herein, a fluid line). In some embodiments, sensor probe 5025 is associated with introducer needle 5072 that assists in skin puncture for insertion of sensor probe 5025. The sensor introducer needle 5072, in some embodiments, at least partially surrounds the sensor probe 5025 while the sensor probe 5025 is inserted into the patient.

  In other embodiments, the injection device 5010 is a needle and does not require the introducer needle 5240. In these embodiments, the infusion device 5010 is inserted into the patient and the septum 5060 is sealed with a fluid source.

  In both FIGS. 86A and 86B, a force is applied to the bridge 5070 in response to both the infusion device 5010 and the sensor probe 5025 being properly aligned. This forces both infusion device 5010 and sensor probe 5025 into the patient. Upon entering the patient, release device 5052 is actuated through the hole, further separating infusion device 5010 and diaphragm 5060 from sensor base 5023 from bridge 5070. Referring to FIG. 86B, when introducer needles 5240 and 5072 are used, they typically remain attached to bridge 5070 after insertion.

  The bridge can be made of any desired material, including plastic. The cannula can be any cannula in the art. The diaphragm 5060 is made of rubber or plastic and can have any design that can provide the desired function. In embodiments where the infusion device is a needle, any needle may be used. In embodiments where an introducer needle is used, any needle, needle device, or introducer device can be used.

  The infusion and sensor assembly requires an applied force for insertion into the patient. Similarly, the infusion and sensor assembly requires the infusion device and sensor to be released from the infusion and sensor assembly. Thus, both force and release can be activated manually. That is, a person may perform these functions or use an insertion device to properly operate the assembly. Referring now to FIGS. 87A-87E, an example of a manually operable insertion device 5011 is shown. The infusion device 5010 and sensor 5023 are held by a bridge 5070. The insertion device 5011 includes a cover 5012 for both the injection device 5010 and the sensor 5023. 87B-87E, using the insertion device 5011, both the injection device 5010 and the sensor 5023 are inserted through the device 10. Although FIG. 87A shows the sharpened portion disassembled, in some embodiments, the cover 5012 completely encases the sharpened portion prior to the insertion process.

  The insertion device 5011 can be operated manually, but can also be incorporated into another insertion device so that mechanical advantages can be applied. 88A-88B, one embodiment of an insertion device 5013 is used with an instrument similar to the insertion device 5012 shown in FIGS. 87A-87E. The mechanism of the insertion device 5013 is shown in FIGS. Actuating lever 5014 provides another mechanical advantage to release the spring (as shown in FIGS. 88C-88D) or to insert insertion device 5012 through a device (not shown). Accordingly, the insertion device 5012 releases the injection device 5010 and the sensor 5023, and then the insertion device 5012 is removed from the insertion device 5013 and the insertion device 5013 is refilled or the insertion device 5013 and the insertion device 5012 are discarded. Can be done.

  Various insertion devices are described herein. However, in other embodiments, a different insertion device is used, or the infusion device and sensor are introduced manually.

  Features for securing the infusion and sensor assembly 5040 to the automatic insertion device may be included. For example, the release device shown in FIGS. 86A-86B as 5052 may receive a pin of an automatic insertion device. Referring to both FIGS. 89A and 89B, an exemplary embodiment of an automatic insertion device 5100 is shown. As shown in the front view of FIG. 89A, the insertion device 5100 includes a pin 5130 that moves in a pin slot 5140 in the insertion cartridge recess 5120. In practice, the injection and sensor assembly (not shown, shown as 5040 in FIGS. 86A and 86B) is pushed into the cartridge recess 5120 and the pin 5130 is inserted into the hole in the injection and sensor assembly (shown as 5052 in FIGS. 86A and 86B). Let it be inserted. As shown in the rear view of FIG. 89B, a cocking lever 5145 is used to prepare for firing the insertion device 5100. The insertion device 5100 is then held against the skin or aligned with the cannula housing and sensor housing on the base (not shown) and fired by depressing the trigger 5110. Upon firing, pin 5130 moves within slot 5140, thereby pressing the infusion device and sensor (both not shown) into the patient. The inserter platform 5160 limits the infusion and downward movement of the sensor assembly. The insertion device may also automatically retract the introducer needle (not shown, see FIG. 86B) from the infusion and sensor assembly.

  The infusion and sensor assembly may be pre-placed on the insertion device 5100 prior to distribution to the end user. As shown in FIG. 90, in other embodiments, a cartridge 5080 may be used to protect the user and further protect the sharps held within the assembly shown as 5040 in FIGS. 56A and 56B. . Referring to FIGS. 90, 86A-86B, and 89A, in a cartridge embodiment 5080, the infusion and sensor assembly 5040 is contained within the cartridge 5080. The cartridge 5080 is mounted in the cartridge recess 5120. The pin 5130 may protrude from the hole 5052 into the groove 5090 in the cartridge 5080. In response to actuation of the insertion device 5100, the pin moves in the groove 5090 as the 5080 moves to the patient to insert the sharps. The cartridge 5080 may be constructed from a rigid material.

  Referring now to FIGS. 91A-91C, there are shown several views of an embodiment of an inserter mechanism for an inserter, such as that shown as 5100 in FIGS. 89A and 89B. 91A shows a perspective view of one embodiment of an insertion device mechanism, FIG. 91B shows a front view, and FIG. 91C shows a side view. The insertion device 5100 has a cocking lever 5145 that is connected to the hammering cocking slide 5330 via the cocking coupling 5350 and used to move the cocking slide 5330 to the loading position. The power spring 5390 connects the hammering cocking slide 5330 to the trigger 5110 and provides the downward force required for insertion of the infusion device or infusion and sensor assembly (not shown) during compression. The trigger hammer 5340 is disposed under the hammer hammer cocking slide 5330 and between the pair of cocking coupling portions 5350. The trigger hammer 5340 transmits kinetic energy released from the power spring 5390 in response to depression of the trigger 5110. The excited trigger hammer 5340 gives an impact to the cartridge bolt 5380 located below. The cartridge bolt 5380 is coupled to, for example, a cartridge housing 5370 that holds the cartridge shown in FIG. Further, the cartridge bolt 5380 is disposed on the upper part of the return spring 5360 for returning the cartridge housing 5350 to the contracted position.

  FIGS. 92A-92F schematically illustrate the temporal sequence for pulling and firing a hammer of an insertion device 5100 of the type described with reference to FIGS. 91A-91C. FIG. 92A shows the insertion device 5100 in the rest position. By lowering the cocking lever (not shown, see FIG. 91A5145), the hammer strike cocking slide 5330 is lowered and the trigger hammer 5340 is engaged. FIG. 92B shows the hammer strike cocking slide 5330 in the lowered position engaged with the trigger hammer 5340. Raising the cocking lever raises the striker cocking slide 5330 and striker 5340, thus compressing the power spring 5390 and the resulting position is shown in FIG. 92C. After securing the proper position of the insertion device 5100 relative to the base (not shown) and / or the patient's skin, the trigger is depressed, thereby sending the trigger hammer 5340 downward. FIG. 92D shows the trigger hammer 5340 in transit. As shown in FIG. 92E, trigger hammer 5340 impacts cartridge bolt 5380, moves it downward, inserts a needle or needles held in a cartridge housing (not shown), and returns spring. Compress 5360. FIG. 92F shows the return spring 5360 in the process of biasing the cartridge bolt 5380 to the information. This causes contraction of the cartridge housing and the cartridge (not shown) contained therein, as well as any associated introducer needle used.

  93A-93C, one embodiment of a time sequence for inserting and securing an infusion device (ie, cannula or needle 5010) to the base Y is shown. FIG. 93A shows a base Y with a locking feature 5210 located on top of the cannula housing 5030. Base Y is typically positioned relative to the skin of patient 5220 when injecting device or cannula 5010 is inserted. FIG. 93B shows a cannula 5010 press fit into the base Y through the cannula housing 5030. In this figure, an introducer needle 5240 is used that traverses a septum (not shown) and is coaxial with cannula 5010. The sharp tip of the introducer needle 5240 emerges from the tip (not shown) of the cannula 5010 and assists in puncturing the patient 5220. The resilient locking feature 5210 is pushed aside during insertion of the cannula 5010. FIG. 93C shows the cannula 5010 fully inserted through the base Y cannula housing 5030 with the tip of the cannula fully inserted into the patient 5220. Introducing needle 5240 is removed and diaphragm 5060 is self-sealing with respect to a fluid source or fluid line (not shown). The resilient locking feature 5210 is engaged with the cannula 5010, thereby preventing the cannula 5010 from moving in conjunction with the base Y. 93A-93C show a cannula 5010, the infusion and sensor assembly shown in FIG. 86B can also be inserted using the locking feature 5210 and method shown and described in FIGS. 93A-93C.

  Referring now to FIGS. 92G-92H, there is shown an insertion cartridge bolt locking mechanism for use with an insertion device, such as that shown in FIGS. 91A-92F as 5100. The cartridge bolt locking mechanism functions as an interconnecting device and can prevent accidental firing while the mechanism is pulling the hammer. The locking mechanism includes a pawl 5420 that prevents downward movement of the cartridge bolt 5380 when engaged in the pawl recess 5410. As shown in FIG. 92G, when the cocking lever 5145 is in the closed position, the cocking lever 5145 contacts the pawl lever 5440 that rotates the pawl 5420 and prevents the pawl 5420 from being inserted into the pawl recess 5410. The pawl spring 5430 disposed between the pawl 5420 and the pawl spring support 5450 is in the compressed position. The cartridge bolt 5380 and trigger hammer 5340 move freely. As shown in FIG. 92H, when the cocking lever 5145 rotates to a lower position, the pawl lever 5440 is released, thereby causing the pawl spring 5430 to have the pawl 5420 recessed (where the pawl 5420 is shown inside the recess). , The recess is press fit into (shown as 5410 in FIG. 92G). The downward movement of the cartridge bolt 5380 is thereby prevented. Next, when the cocking lever 5145 is returned, the pawl 5420 is returned to the non-locking position. The cartridge bolt 5380 is then free for downward movement in the trigger process.

  Referring now to FIGS. 94A-94C, the cannula is a conventional cannula (as shown in FIG. 86B) that requires an introducer needle to the base Y to establish fluid communication with the fluid line 310. One embodiment of a process for fitting cannula 5010 is shown. FIG. 94A shows a cross-sectional view of a cannula 5010 having two diaphragms (introducing needle diaphragm 5062 and fluid line diaphragm 5270). Introducing needle septum 5062 seals passage 5280 leading to the hollow needle of cannula 5010 (not shown, shown as 5290 in FIG. 94B). Cannula introducer needle 5240 is shown positioned on introducer needle diaphragm 5062 just prior to introduction of introducer needle 5240.

  Referring now to FIG. 94B, introducer needle 5240 is shown penetrating introducer needle diaphragm 5062. The user inserts the cannula 5010 into the base Y (with the rigid hollow needle 5290 pointing upwards). When inserting cannula 5010 into base Y, introducer needle 5240 punctures fluid line diaphragm 5270 and establishes fluid communication between fluid line 310 and passageway 5280. When the cannula 5010 is inserted into the base Y, holding the base Y against the patient (not shown), fluid communication between the fluid line 310 and the passage 5280 is established at about the same time as it penetrates the patient's skin. The Referring now to FIG. 94C, cannula 5010 is shown fully inserted into base Y with the introducer needle removed and fluid communication with fluid line 310 established.

  In an alternative embodiment, insertion of the infusion device and / or sensor is assisted by a vibration motor that is associated with the fluid delivery device. Simultaneously with insertion of the infusion device and / or sensor, the vibration motor may be activated.

(adhesive)
Referring now to FIG. 95, a top perspective view of one embodiment of an adhesive patch 3100 for securing the fluid delivery device 10 etc. to the skin of a patient (not shown) is shown. The adhesive patch 3100 is shown in the shape shown, but other shapes can be used. Any adhesive patch 3100 that can hold the fluid delivery device can be used.

  The fluid delivery device 10 is held by the adhesive member 3111 under the central region 3130 of the adhesive patch 3100 that is attached to the patient's skin. These adhesive members 3111 radially extend from the central region 3130 and are separated from each other by interposing the region 3121. The radial arrangement of the adhesive members 3111 allows the device 10 to be fixedly attached to the patient. In some embodiments, the central region 3130 covers the entire device 10, however, in other embodiments, the central region 3130 covers a portion of the device 10. Central region 3130 may also include interlocking adhesive features (not shown) that may be retained by complementary interconnect features (not shown) of device 10. In an alternative embodiment, the device 10 is secured to the top of the central region 3130 (eg, by an adhesive or interconnect feature).

  The adhesive patch 3100 is typically flat and consists of a polymer sheet or fiber. The adhesive patch 3100 may be supplied with an adhesive attached to one side, and may be protected by a peelable backing such as a peelable plastic sheet to which the adhesive adheres more loosely than the patch 3100. The backing may be a single continuous piece or may be divided into regions that can be removed separately.

  In an illustrative embodiment, the backing of the central region 3130 may be removable without removing the backing of the adhesive member 3111. To use the adhesive patch 3100, the user removes the backing of the central region 3130 and presses the device 10 against the newly exposed central region adhesive to adhere the device 10 to the central region 3130. The user then places the device on the skin, removes the backing from the adhesive member 3111, attaches the adhesive member to the skin, and repeats the attachment process with the additional member. The user may secure all of the adhesive members 3111 or only a part of the members to attach and attach the additional adhesive member 3111 to another day. Typically, the adhesive used for adhesion to the skin has a fixed duration of only a few days, so a set of adhesive members 3111 should be applied on different days (for example, every 3 to 5 days). This extends the time that the device 10 remains attached to the skin, reducing the time, expense, and discomfort often associated with reapplying the device. The variable tab may have indicators such as different colors or numbers indicating the appropriate time to apply the various adhesive members 3111. The adhesive member 3111 may include perforations and provide vulnerability to the central region 3130 so that the used adhesive member can be removed after use. Additional embodiments for extending the period during which the device 10 remains attached are discussed above with reference to FIGS.

  FIG. 96 schematically shows a cross-sectional view of the fluid delivery device 10 with the cannula 5010 inserted and held under the adhesive patch 3100. A pad 3220 may be included between the device 10 and the patient's skin 3250 to allow air to flow through the skin. The air flow to the skin may be increased by including a passage 3230 in the pad 3220. The passage 3230 may also be formed by using a plurality of spaced pads or by constructing the pad 3220 from a highly porous material. Thus, the pad 3220 can be any shape and size, and in some embodiments, the pad 3220 consists of several separate pieces. The pad 3220 may be adhered to the bottom surface of the device 10 during manufacture or may be adhered to the device 10 by a user. Alternatively, pad 3220 may be loosely placed on the skin by the user prior to application of adhesive patch 3100. The pad 3220 may include a flexible material such as a porous polymer foam.

  FIG. 97 illustrates an embodiment of the present invention using a first adhesive patch 3100 and an additional adhesive patch 3300 to secure a device (not shown) to a patient. Initially, a device (not shown) is positioned for use and secured to a patient's skin (not shown) with an adhesive patch 3100 using a tab-like adhesive member 3111. The central region 3130 may be positioned at the top (as shown) or may be fixed under the device. After a certain period of time, the elongated or short second adhesive patch 3300 is positioned so that its central region is placed on top of the first adhesive patch 3100 and the second adhesive patch adhesive member 3320 is attached to the first adhesive patch 3100. It is fixed to the patient's skin in the intervening region between the adhesive members 3111 of the adhesive patch. A fragile region may be provided to assist in removing loose or undesirable adhesive members 3111 associated with previously placed patches 3100.

  Referring now to both FIGS. 98 and 99, an embodiment is shown in which the adhesive patch 3100 is divided into at least two small adhesive patches. In these embodiments, the adhesive patch 3100 is divided into two adhesive patches (3410 and 3420), each having an adhesive member 3111 arranged radially around the central gap 3430. The two adhesive patches (3410 and 3420) each extend in a semicircle of about 180 °, but other configurations such as three patches each extending 120 ° or four patches each extending 90 ° can also be used. is there. In some embodiments, the adhesive can include more than four patches. The configuration described for these embodiments follows the equation 360 ° / n, where n is the number of patches. However, in other embodiments, depending on the shape of the device, the formulas shown and the description herein do not apply. In yet other embodiments, the patch may also cover more than 360 ° and thus may overlap.

  As shown in the perspective view of FIG. 99, due to the presence of a central air gap (not shown, shown in FIG. 98), the central region 3130 is in the form of a strip for bonding and positioning along the periphery of the device 10. . Both patches (3410 and 3420) secure device 10 to the skin (not shown). As in the embodiment described with reference to FIG. 95, air may flow between the adhesive members 3111 and under the device 10 (particularly where a passage 3230 is provided).

  FIG. 100 shows a perspective view of an embodiment that includes using a plurality of adhesive patches to extend the time that the device 10 remains adhered to a patient (not shown) prior to removal. Even if one of the plurality of partial adhesive pads 3420 is removed, the device 10 remains in place (by the residual adhesive patch 3410 and / or by the user). The removed adhesive patch 3420 is then replaced with a new replacement adhesive patch (not shown). The replacement adhesive patch may be homogenous with the removed pad 3420 or has an adhesive member 3111 positioned in an alternative configuration that adheres to new skin between the areas previously covered by the adhesive patch 3420. May be. The remaining adhesive patch 3410 may then be replaced in a similar manner. An index such as color identification may be used to indicate the usage period of the adhesive patch. The patch may have a color change mechanism that indicates that the service life has elapsed. Decorative patterns such as images and designs may be included on the patch.

  FIG. 101 schematically illustrates an embodiment in which a plurality of adhesive members 3111 are attached to the patient 12 and are also connected via a tether 3730 to a ring-shaped central region 3130. The tether 3730 may be a fiber or string and may be elastic to reduce movement of the device 10 in response to movement of the patient 12. Also, the use of tether 3730 increases the options available for the skin location of adhesive member 3111.

  The adhesive used in the embodiment described in FIGS. 95-101 can be any effective and safe adhesive that can be used on the patient's skin. However, in one embodiment, the adhesive used is a useful spunlace medical nonwoven tape of 3M product number 9915.

(Clamp and latch)
102A-102C schematically illustrate one mechanism for biting or latching the top and base of the fluid delivery device together. Referring initially to FIG. 102A, an elevation view of clamp 6410 is shown. FIG. 102B shows a base Y with a keyhole 6440 for two clamps. A corresponding keyhole may be included in the upper part (not shown). Referring now to FIG. 102C, the top X and base Y may be aligned and a clamp 6410 may be inserted through the keyhole (not shown, shown as 6440 in FIG. 102B). By rotating the clamp 6410 by 90 °, the stud bar 6430 is moved to the locking position. By depressing the cam lever 6400, the cam 6415 screwed to the clamp pin 6420 is engaged, and the upper part X is pushed. As a result, the upper portion X and the base portion Y are held by the biting force between the cam 6415 and the stud bar 6430. By pushing up the cam lever 6400, the biting force is released and the clamp 6410 may be rotated 90 ° and pulled back to disassemble the top X and base Y. In some embodiments, the lever may act as a protective cover for the top X.

  An alternative embodiment for holding a portion of the device together is shown in FIGS. 103A-103D. 103A shows a perspective view of the cam guide 6500, and FIG. 103B shows a top view. The cam guide 6500 has a keyhole 6440 and an inclined surface 6510. FIG. 103C shows a cam follower 6520 having a central pin 6540 with a head 6560 attached to the first end and a bar 6550 attached to the other end. As shown in the cross-sectional view of FIG. 103D, the cam follower (not shown, shown in FIG. 103C) penetrates the top X, base Y, and keyhole (not shown, shown in FIG. 103C) of the cam guide 6500. May be. The movement of the lever 6530 attached to the central pin 6540 causes rotation of the cam follower (not shown, shown in FIG. 103C), causing the bar 6550 to follow an inclined surface (not shown, shown as 6510 in FIG. 103C). , Thereby converting the rotational force into a force that firmly grips the base Y and top X between the cam follower head 6560 and the bar 6550.

(Reservoir)
An exemplary embodiment of a collapsible reservoir for holding fluid is shown in FIGS. 104-106C. The collapsible reservoir has at least one compartment or wall in which fluid is drawn and folded, thereby maintaining ambient pressure therein.

  In most embodiments, a sealed port (eg, a diaphragm) is included in the reservoir. The port allows the reservoir to be filled with fluid by a syringe and allows a fluid line without leakage. Alternatively, an adapter may be used to connect the reservoir to the fluid line. Alternatively, as described above with reference to FIG. 71, a needle may be associated with the reservoir and a septum may be associated with the end of the fluid line. The reservoir may be made of a known plastic material that is compatible with the fluid contained in the reservoir, even for a short period of time. In some embodiments, the reservoir is generally foldable, i.e., the reservoir does not include a rigid body surface.

  Referring now to FIG. 104, a cross-sectional view of the reservoir 20 is shown. A cavity 2645 for holding the fluid volume is formed between the rigid reservoir body 6200 and the flexible reservoir membrane 6330. A flexible membrane 6330 is hermetically attached around the cavity 2645 and retains fluid in the cavity 2645. A flexible membrane 6330 provides foldability to the reservoir 20. As fluid is pumped from cavity 2645, it deforms inward.

  The diaphragm 6270 is seated on a neck 6240 that extends from the body 6200. The diaphragm 6270 serves as an interface between the cavity 2645 and the fluid line. In some devices, the fluid line terminates in a needle (not shown). In these embodiments, the needle may be inserted into the septum 6270 to access the needle chamber 6280 portion of the cavity 2645. The position of the diaphragm 6270 can be maintained between the cap 6250 and a protrusion (not shown) formed at the joint between the inner wall 6281 of the needle chamber 6280 and the cap port 6282. The cap 6250 may be held by a friction fit within the cap port 6282. With the insertion of the cap 6250, its position is limited by the wall 6261 of the cap port 6282. The portion of the cap 6250 closest to the diaphragm 6270 may have a central opening to allow insertion of a needle that penetrates the diaphragm 6270 through the cap 6250. Alternatively, cap 6250 may be punctured by a needle.

  FIG. 105 shows a perspective view of the inside of the foldable reservoir 20. Edge 6230 allows for the attachment of a flexible reservoir membrane that can be applied by welding, biting, gluing, or other suitable method, creating a fluid tight seal. A protective structure 6290 may be included to allow fluid to flow into or out of the cavity 2645, but prevents the needle from entering the cavity, thereby preventing the possibility of puncture of the reservoir membrane.

  106A-106C illustrate an alternative embodiment of a reservoir in which a cap 6250 seals and adheres the septum 6270 to the reservoir wall 6320. The wall 6320 can be made of, for example, a flexible sheet of PVC, silicone, polyethylene, or an ACLAR film. In some embodiments, the wall 6320 may consist of a thermoformable polyethylene laminate formed of an ACLAR film. The flexible sheet is compatible with the fluid. The wall may be attached to a rigid housing or part of a flexible plastic pouch that may be formed by bending and welding both ends of a plastic sheet. FIG. 106A shows a cap 6250 that is sealed to the wall 6320 via circular fins 6350. The diaphragm 6270 may be inserted into a turret 6340 that protrudes from the cap 6250. The turret 6340 may be made of a material such as low density polyethylene that is deformed at high temperatures but is rigid at room temperature, for example. Referring now to FIG. 106B, the turret 6340 on the diaphragm 6270 is melted or bent using a hot press 6310, or another instrument, or a melting process. Referring now to FIG. 106C, the diaphragm 6270 is shown secured to the cap 6250.

  Certain fluids are sensitive to storage conditions. For example, insulin is somewhat stable in glass vials (typically when shipped), but may become unstable after prolonged contact with certain plastics. In some embodiments, the reservoir 20 is made of such plastic. In this case, the reservoir 20 may be filled with a fluid immediately before use so that the fluid and the plastic come into contact with each other for a short time.

(Reservoir filling station)
Referring now to FIG. 107, a reservoir filling station 7000 for filling the reservoir 20 with fluid is shown. Fluid may be withdrawn from its original container with a syringe 7040 and introduced into the reservoir 20 using a filling station 7000. The filling station 7000 may include a substantially rigid filling station base 7010 that is screwed to a substantially rigid filling station cover 7020 via a hinge 7030. Thus, the stand 7000 can be opened and closed to receive and hold the reservoir 20. The needle 7050 attached to the syringe 7040 may then penetrate the fill opening 7060 in the cover 7020 and the reservoir septum 6270. Because the filling station cover 7020 is rigid, it sets the movement limit by the syringe 7040, thus controlling the puncture depth of the needle 7050 into the reservoir 20 and preventing puncture into the reservoir 20 bottom surface. The leg 7070 holds the stand 7000 in an inclined position when supported on a certain surface. Since the stand 7000 is inclined, when fluid is injected from the syringe 7040 into the reservoir 20, the air tends to rise upward to the diaphragm 6270. After syringe 7040 has injected a desired amount of fluid into reservoir 20, syringe 7040 may be used to remove residual air in reservoir 20. Because the filling station base 7010 and the cover 7020 are rigid, the flexible reservoir 20 is generally unable to expand beyond a fixed volume and overfilling of the reservoir 20 is prevented. Base 7010 and cover 7020 may be locked together with a clasp, or a heavy cover may be used to further prevent overexpansion and overfilling of the reservoir.

  108A and 108B, an alternative embodiment of a reservoir filling station 7000 is shown. In this embodiment, a reservoir (not shown) is placed in the space between the cover 7020 and the base 7010. Hinge 7030 is attached to cover 7020 and base 7010. As shown in FIG. 108B, the reservoir (not shown) is on the inside and a syringe (not shown) needle (not shown) is inserted into the fill opening 7060. Fill opening 7060 is directly connected to the reservoir diaphragm (not shown). Confirmation window 7021 shows a fluid line based on the volume of fluid injected into the reservoir.

  A fluid delivery system typically includes a fluid delivery device and an external user interface, although in some embodiments a complete or partial internal user interface is included within the device. The device can be any device described herein or variations thereof.

  FIG. 109A shows a flow diagram of a data acquisition and control scheme for an exemplary fluid delivery system embodiment. The patient or caregiver utilizes an external user interface 14, which is typically a base station or portable device that is stored separately from the fluid delivery device 10. In some embodiments, the user interface 14 is integrated with a computer, mobile phone, mobile terminal, or other consumer device. The user interface assembly may perform continuous or intermittent data communication with the fluid delivery device 10 via wireless communication (eg, a standard wireless protocol such as LF, RF, or “Bluetooth”), but also data It can also be connected via cable, optical connection, or other suitable data connection. The external user interface 14 communicates with the processor 1504 and inputs control parameters such as weight, fluid dosage range, or other data, occluded flow, leakage, empty reservoir, battery failure, maintenance needs, lifetime Status and function updates are received, such as the presence of an error condition resulting from the course of time, total fluid delivery, or remaining or incorrect disposable components. The interface 14 may send an error signal to the patient monitor or medical professional through a telephone, email, pager, instant message, or other suitable communication medium. The reservoir actuator assembly 1519 includes an actuator 1518 and a reservoir 1520. Dispensing assembly 120 transmits data regarding flow from the flow line to processor 1504. The processor 1504 uses the flow data and adjusts the action of the actuator 1518 to increase or decrease the flow rate from the reservoir pump assembly 1519 to approximate the desired dose and timing. Optionally, the feedback controller 1506 of the processor 1504 may receive data related to the operation of the reservoir pump assembly 1519 for condition detection such as an open or short circuit fault or actuator temperature.

  FIG. 109B shows an alternative embodiment of the process diagram in FIG. 102A. In this embodiment, the lack of a dispensing assembly / sensor eliminates feedback based on fluid volume.

  Referring now to FIG. 110A, a process diagram of one embodiment of the overall operation of the fluid delivery device within the fluid delivery system is shown. The user initiates the system 2800 using a switch or external user interface form (step 2800). The system reads default values, activates system tests (step 2810), and initializes by determining variable parameters such as desired steady state and bolus amount. The variable parameters may be selected by the user using the user interface using an input device such as a touch screen on the user interface or by reading stored parameters from memory (step 2820). Actuator timing is calculated based on the predicted or calibrated performance of the fluid delivery device (step 2830). The dispensing assembly is started at the start of activation of the fluid delivery device (step 2840). Dispensing assembly data collection 2835 continues through actuation and delivery. During operation, the dispensing assembly provides data and allows measurement of the accumulated fluid volume as well as the flow rate that has flowed through the dispensing chamber for over an hour. The fluid delivery device is activated to flow fluid from the flow line to the dispensing chamber (step 2840). Due to the exit impedance, in some embodiments, the drug flows from the dispensing chamber to the patient at a rate defined by the force applied by the diaphragm spring and by the force applied by the pumping assembly (step 2860). If the reservoir is determined to be empty based on user interruption, low flow condition, predicted accumulated flow rate or detection by additional reservoir volume sensor, or any other alarm action as part of the system or user specified The system stops and the user is notified (step 2870). In the absence of a user stop signal, confirmation of an empty reservoir, or another alarm indication, actuator timing adjustments may be required due to deviations between actual and desired flow rates, or due to user-desired flow rate changes. A check is made to determine whether or not (step 2880). If no adjustment is required, the process returns to step 2840. If adjustment is required, the process returns to step 2830 instead.

  Referring now to FIG. 110B, a flowchart of another embodiment of the overall operation of the fluid delivery device within the fluid delivery system is shown. In this embodiment, the determination of the actuation timing adjustment is made based on a user input variable or another feedback. In this embodiment, a dispensing assembly with a sensor for measuring volume is not included. Thus, adjustments are made based on an alternative feedback mechanism.

(Wireless communication)
Referring now to FIG. 111, an embodiment layout is shown using coils for inductive charge and wireless communication within a fluid delivery system. As described above, the user interface assembly 14 can be embodied as a portable user interface assembly 14 that is in wireless communication with the fluid delivery device 10. A secondary coil (ie, solenoid) 3560 may be employed within the fluid delivery device 10 as a wireless transceiver antenna in conjunction with the wireless controller 3580. Also, secondary coil 3560 may serve as a secondary transformer for charging device battery 3150 at least partially in conjunction with battery charging circuit 3540. In this embodiment, user interface assembly 14 includes a primary coil 3490 for inductively coupling energy to secondary coil 3560. When the user interface assembly 14 is proximate to the fluid delivery device 10, the primary coil 3490 excites the secondary coil 3560. The excited secondary coil 3560 provides power to a battery charging circuit 3540 for charging the battery 3150 within the fluid delivery device 10. Also, in some embodiments, primary coil 3490 functions as an antenna and works in conjunction with radio controller 3470 to send information to and receive information from fluid delivery device 10.

  Referring now to FIG. 112, some embodiments include long-range wireless communication (eg, 20-200 feet or more) hardware within the fluid delivery device 10. Thus, the fluid delivery device 10 can be monitored remotely.

  Still referring to FIG. 112, the patient-mediated intermediate transceiver 6600 typically provides the benefits of long-range communication without increasing the size, weight, and power consumption of the fluid delivery device 10. Is possible. As shown in the data process diagram of FIG. 112, wearable fluid delivery device 10 uses short-range hardware and associated software to send data to or receive data from intermediate transceiver 6600. For example, the device 10 may be equipped to transmit data over a distance of about 3-10 feet. The intermediate transceiver 6600 may then receive this data and relay this data to the user interface assembly 14 using long distance hardware and software. The intermediate transceiver 6600 may also receive control signals from the user interface assembly 14 and relay these signals to the device 10. Also optionally, the user interface assembly 14 may be in direct communication with the fluid delivery device 10 when in range. This direct communication may be configured to occur only when the intermediate transceiver 6600 is not detected, or otherwise, whenever the user interface assembly 14 and the fluid delivery device are within range of each other.

Many types of data may be transmitted in a manner that includes, but is not limited to:
Data regarding pump actuation timing and volume measurements, as well as other data from the dispensing assembly, may be sent to the intermediate transceiver 6600 and thereby to the user interface assembly 14.
The alarm signal is transmitted to and from the fluid delivery device 10.
A signal for confirming receipt of data may be transmitted from the user interface 14 to the intermediate transceiver 6600 and from the intermediate transceiver 6600 to the fluid delivery device 10.
Control signals for changing the operating parameters of the device 10 may be transmitted from the user interface assembly 14 to the fluid delivery device 10 using the intermediate transceiver 6600.

  Referring now to FIG. 113, a plan view of a particular embodiment of the intermediate transceiver 6600 is shown. Short range transceiver 6610 communicates with nearby fluid delivery devices. The device's short range transceiver and intermediate transceiver 6600 may communicate using one or more of many protocols and transmission frequencies known to be useful for short range communication, eg, wireless communication. Good. Data received by the intermediate transceiver 6600 is communicated to a microprocessor 6630 that stores the data in a memory 6620 (eg, a flash memory chip) and can read the data as needed. The microprocessor 6630 is also connected to a long distance transceiver 6640 that is in data communication with the user interface. For example, the intermediate transceiver 6600 and user interface assembly may operate with the Bluetooth standard, a spread spectrum protocol that uses a radio frequency of about 2.45 MHz, and may operate over a distance of up to about 30 feet. . The Zigbee standard is an alternative standard that operates in the ISM bands of approximately 2.4 GHz, 915 MHz, and 868 MHz. However, any wireless communication can be used.

Optionally, the microprocessor 6630 analyzes the received data to detect the presence of malfunctions or maintenance requirements associated with the device. Some examples of fault conditions include, but are not limited to:
Lack of received data within the time exceeding the set limit.
Lack of data acknowledgment signal from the device or user interface assembly.
Overflow of device internal memory 6620 or a state close to overflow.
Low power.
An excessively high, low, or inappropriately timed volume measurement received from the fluid delivery device 10.

  Based on this failure analysis, the microprocessor 6630 may trigger an alarm 6650 (eg, a bell or buzzer). Microprocessor 6630 may also communicate alarm conditions to a remote device. The remote device may be, for example, a user interface assembly using a long range transceiver 6640, a fluid delivery device 10 using a short range transceiver, or both a user interface assembly and a fluid delivery device. In response to receiving the alarm signal, the user interface assembly may relay the alarm signal to a medical professional or patient monitor over a long distance (eg, by a pager or telephone, or other communication method).

  The power source 6670 is rechargeable and may store sufficient energy to operate continuously for a period of time, eg, at least 10 hours. However, the operating time will vary based on the application and device. The fluid delivery device may be reduced in size and placed in a pocket, handbag, briefcase, backpack, etc. for easy carrying. One embodiment of the device includes means for resistance to daily impact or spills. Some embodiments include decorative features, or any feature of a wide range of consumer electronics such as playing video games, sending and receiving instant messages, watching digital video, playing music, etc. Additional features may be included, without limitation. Use of such features may be excluded or restricted for several hours of the day or throughout the day, including third party control equipment. Alternatively, the device may be as small and simple as possible and only serve to repeat short distance signals over long distances. For example, the memory and analysis function may be omitted.

  Referring now to FIG. 114, a data process diagram for an embodiment of the present system is shown. The intermediate transceiver 6600 operates as a general patient interface that communicates with multiple devices and relays information from those devices over a long distance to one or more user interfaces associated with the devices. Shown to do. Examples of devices include fluid delivery systems, glucose sensors, knee joints with integrated strain sensors, device mounted enteric probes in tablet form, defibrillators, pacemakers, and other wearable therapeutic delivery devices, etc. Including wearable, implantable, or internal medical devices. Intermediate transceiver 6600 supports hardware (eg, multiple antennas and circuits), as well as multiple protocols, because different types of devices and devices from different manufacturers may utilize different short-range communication standards and frequencies. Software may be included.

(Battery charger)
115 and 116, one embodiment of an instrument for charging the battery 7100 is shown. In FIG. 15, the upper non-disposable portion of the fluid delivery device 2620 is shown cut from the disposable portion of the base of the fluid delivery device. The charger 7100 is used to charge a battery (not shown) in the upper portion 2620. In FIG. 116, the upper portion 2620 is shown on the charger 7100. The latch 6530 is closed and is shown with the upper portion 2620 connected to the charger 7100. Accordingly, the latch 6530 used to connect the top 2620 to the base (not shown) is also used to connect the top 2620 to the charger 7100. By docking, a direct power connection may be established or power may be transmitted by inductive coupling. Also, in some embodiments of the system, the patient employs a plurality of non-disposable portions 2620 in turn. That is, a second non-disposable part (not shown) is used while charging one non-disposable part 2620.

  Various embodiments described herein include, for example, pump structures, pump actuators, volume sensors, flow restrictors, reservoirs (and reservoir interfaces), sharp inserters, housings, latching mechanisms, user interfaces, Different types and components of components such as mounting peripherals (eg, control devices, processors, power supplies, network interfaces, sensors) and other peripheral devices (eg, portable remote control devices, base stations, repeaters, filling stations) including. Note that alternative embodiments may incorporate various combinations of such elements. Thus, for example, the pump structure described with reference to one embodiment (e.g., the pump illustrated and described with reference to FIGS. 15A-15D) can be used in any of various configurations of pump actuators (e.g. Single shape memory actuator with mode, single shape memory actuator with multiple modes of operation, multiple shape memory actuators of the same or different sizes), and other elements in various combinations (Or lack of other elements) and / or may be used in devices with any variety of flow restrictors.

  Further, although various embodiments are described herein with reference to non-pressurized reservoirs, pressurized reservoirs may be used in certain embodiments or under certain conditions (eg, during priming and / or air evacuation). Note that may be used in In particular, the pressurized reservoir may facilitate filling of the pump chamber, for example, after contraction of the pumping actuation member 54 shown and described with reference to FIGS.

  Further, although various embodiments are described herein with reference to a pump motor disposed in a reusable portion of the housing, the pump and / or pump motor may otherwise be, for example, a fluid It should be noted that it may be positioned in a disposable part with various components in contact with it. As with some other motors described herein, the motor disposed in the disposable portion may include one or more shape memory actuators.

  Note that headings are included for convenience and are not intended to limit the scope of the invention.

  In various embodiments, the methods disclosed herein, including methods for controlling and measuring fluid flow rates, and methods for establishing communication between coupled components, can be used with suitable controllers or other devices. As a computer program product for use with a computer system (generally referred to herein as a “computer system”). Such an implementation is fixed on a tangible medium such as a computer readable medium (eg, diskette, CD-ROM, ROM, EPROM, EEPROM, or fixed disk) or connected to a network via a modem or medium. It may also include a series of computer instructions that can be transmitted to the computer system via another interface device such as a communication adapter. The medium may be a tangible medium (eg, optical or analog communication line) or a medium implemented with wireless technology (eg, microwave, infrared, or other transmission technology). The series of computer instructions may embody the desired functionality previously described herein with respect to the system. Those skilled in the art will appreciate that such computer instructions can be written in a number of programming languages for use with many computer structures or operating systems.

  Further, such instructions may be stored in any storage device, such as a semiconductor, magnetic, optical, or other storage device, such as optical, infrared, acoustic, wireless, microwave, or other transmission technology It may be transmitted using any communication technology. Such a computer program product is preloaded with a computer system (eg, system ROM, EPROM, EEPROM, or delivered as removable media with accompanying printing or electronic documentation (eg, commercially available software)) It is expected that it can be delivered from a server or electronic bulletin board over a fixed disk) or via a network (eg, the Internet or World Wide Web). Of course, some embodiments of the invention may be implemented as a combination of both software (eg, a computer program product) and hardware. Still other embodiments of the invention are implemented as entirely hardware or substantially in software (eg, a computer program product).

  It should be noted that the dimensions, sizes, and quantities described herein are illustrative only and the present invention is in no way limited thereto. In an exemplary embodiment of the invention, the patch-sized fluid delivery device is about 6.35 cm (˜2.5 inches) long, about 3.8 cm (˜1.5 inches) wide, and has a height of about 1. Of course, these dimensions may be 9 cm (˜0.75 inch), but these dimensions are merely exemplary, and the dimensions may vary widely for different embodiments.

  Although the principles of the present invention have been described herein, those skilled in the art will appreciate that the description has been made by way of example only and is not intended as limiting the scope of the invention. In addition to the exemplary embodiments shown and described herein, other embodiments are intended to be within the scope of the present invention. Modifications and alternatives by one skilled in the art are considered to be within the scope of the present invention.

The foregoing features of the invention will be more readily understood by reference to the following detailed description, taken in conjunction with the accompanying drawings, in which:
FIG. 1 shows a patient with a patch and a wireless handheld user interface assembly. FIG. 2A is a schematic diagram of a fluid delivery device with a feedback control. FIG. 2B is a schematic diagram of a fluid delivery device with a feedback controller and a reservoir. FIG. 3 is a schematic view of a fluid delivery device having an unpressurized reservoir. FIG. 4A is a schematic cross-sectional view of various embodiments of a flow restrictor. FIG. 4B is a schematic cross-sectional view of various embodiments of a flow restrictor. FIG. 4C is a schematic cross-sectional view of various embodiments of a flow restrictor. FIG. 5 shows an elastic dispensing assembly in series with a flow restrictor. FIG. 6 shows a dispensing assembly having a measurement chamber and a sensor. FIG. 7 shows a dispensing assembly having a measuring chamber with a dispensing spring and a sensor. FIG. 8 shows a cross-sectional view of a dispensing assembly with an alternative acoustic path. FIG. 9 shows a schematic view of the dispensing assembly. FIG. 10 shows a diaphragm spring for use with an elastic variable volume dispensing chamber. FIG. 11A shows an example basal fluid delivery kinetic profile. FIG. 11B shows an exemplary bolus fluid delivery kinetic profile. FIG. 11C shows kinetic data representing normal fluid delivery. FIG. 11D shows kinetic data representing various fault conditions. FIG. 11E shows kinetic data representing various fault conditions. FIG. 11F shows kinetic data representing various fault conditions. FIG. 12 shows a flow diagram for the sensing and reaction process of an embodiment of a fluid delivery device. FIG. 13 shows a block diagram of a fluid line comprising a pressure generating assembly. FIG. 14 shows a block diagram of a fluid line with a valve pump. FIG. 15A shows a schematic view of a pumping mechanism. FIG. 15B shows a schematic diagram of the pumping mechanism. FIG. 15C shows a schematic diagram of the pumping mechanism. FIG. 15D shows a schematic diagram of the pumping mechanism. FIG. 16 shows a schematic view of the pumping mechanism. FIG. 17 schematically shows a cross-sectional view of an embodiment including a shape memory wire actuator capable of multiple pumping modes. FIG. 18 schematically illustrates a cross-sectional view of an embodiment that includes two shape memory actuators and is capable of multiple pumping modes. FIG. 19 schematically illustrates a cross-sectional view of an embodiment that includes shape memory actuators of different lengths. FIG. 20A schematically shows an embodiment for attaching a shape memory actuator. FIG. 20B schematically shows an embodiment for attaching a shape memory actuator. FIG. 21A schematically illustrates an embodiment for attaching a shape memory actuator to a pumping mechanism. FIG. 21B schematically illustrates an embodiment for attaching a shape memory actuator to a pumping mechanism. FIG. 22 shows a pumping mechanism that employs fingers. FIG. 23 shows a pumping mechanism that employs fingers. FIG. 24 shows a pumping mechanism that employs a rotating protrusion. FIG. 25 shows a pumping mechanism that employs a plunger and an outer cylinder. FIG. 26 shows a diagram of the shape memory actuator in an expanded state. FIG. 27 shows a diagram of a shape memory actuator in a contracted state. FIG. 28 shows a view of a pumping assembly employing a plunger and an outer cylinder, and a shape memory motor having a lever. FIG. 29 shows a diagram of a pumping assembly and shape memory motor employing a plunger and an outer cylinder. FIG. 30 shows a diagram of a pumping device employing a plunger and an outer cylinder, and a shape memory motor having a wire in the shaft of the plunger. FIG. 31 shows an embodiment of a flow line comprising a combined pump and reservoir. FIG. 32 schematically shows a cross-sectional view of the valve pump in the rest position. FIG. 33 schematically shows a cross-sectional view of the valve pump of FIG. 32 in an intermediate position. FIG. 34 schematically shows a cross-sectional view of the valve pump of FIG. 32 in the operating position. FIG. 35 schematically shows a cross-sectional view of a pumping diaphragm for use in a valve pump. FIG. 36 shows a perspective view of a diaphragm spring for use in a pumping diaphragm. FIG. 37 schematically shows a cross-sectional view of a valve pump employing a lever and a shape memory wire actuator. FIG. 38 schematically shows a cross-sectional view of an embodiment including a valve pump employing an elastic cylindrical bend. FIG. 39 schematically illustrates a cross-sectional view of an embodiment including a valve pump bend having an elastic member and a rigid support. FIG. 40 schematically shows a cross-sectional view of a stationary valve pump with a diaphragm spring upstream of the flexible membrane. 41 schematically shows a cross-sectional view of the valve pump of FIG. 40 in an intermediate state. FIG. 42 schematically shows a cross-sectional view of the valve pump of FIG. 40 in the activated state. FIG. 43 schematically shows a cross-sectional view of a valve pump provided with a diaphragm spring upstream of the flexible membrane, which is attached to the force applying member in the circumferential direction. FIG. 44 schematically shows a cross-sectional view of a valve pump with a diaphragm spring upstream of a flexible membrane and includes a rigid ball for transmitting force. FIG. 45 schematically shows a cross-sectional view of an embodiment including a valve pump having elastic pump blades. FIG. 46 schematically shows a cross-sectional view of an embodiment, including an alternative to elastic pump vanes for use with a valve pump. FIG. 47 schematically illustrates a cross-sectional view of an embodiment including a valve pump having a plurality of force members. FIG. 48 schematically shows a pumping mechanism including a bell crank driven valve pump and a flow bias valve in a stationary or filling mode. FIG. 49 schematically shows the pumping mechanism of FIG. 48 in the activated state. FIG. 50 schematically illustrates a cross-sectional view of a flow bias valve according to an embodiment of the present invention having a raised valve seat and in a closed position. 51 schematically illustrates a cross-sectional view of the flow bias valve of FIG. 50 in the open position. FIG. 52 schematically illustrates a cross-sectional view of a flow bias valve according to an embodiment of the present invention without an elevated valve seat and in an open position. FIG. 53 schematically shows a cross-sectional view of the flow bias valve of FIG. 52 in the closed position. FIG. 54 schematically shows the forces acting on the poppet near the valve outlet, according to an embodiment of the present invention. FIG. 55 schematically illustrates the force acting on the poppet near the valve inlet according to an embodiment of the present invention in an enlarged view. FIG. 56 schematically illustrates a flow bias valve with adjustable cracking pressure according to an embodiment of the present invention. FIG. 57 shows a schematic diagram of a flow line utilizing an unpressurized reservoir. FIG. 58 shows a schematic diagram of a flow line utilizing an unpressurized reservoir. FIG. 59A shows a schematic diagram of fluid flow within a fluid delivery device. FIG. 59B shows a schematic diagram of fluid flow within the fluid delivery device. FIG. 59C shows a schematic diagram of fluid flow within the fluid delivery device. FIG. 59D shows a schematic diagram of fluid flow within the fluid delivery device. FIG. 59E shows a schematic diagram of fluid flow within the fluid delivery device. FIG. 60A shows an exploded schematic view of fluid flow within a fluid delivery device. FIG. 60B shows an exploded schematic view of fluid flow within the fluid delivery device. FIG. 60C shows an exploded schematic view of fluid flow within the fluid delivery device. FIG. 60D shows an exploded schematic view of fluid flow within the fluid delivery device. FIG. 61A shows a schematic diagram of fluid flow within a fluid delivery device. FIG. 61B shows a schematic diagram of fluid flow in a fluid delivery device. FIG. 61C shows a schematic diagram of fluid flow within the fluid delivery device. FIG. 62A shows a schematic diagram of a stand-alone device. FIG. 62B shows a schematic diagram of a stand-alone device. FIG. 63A shows a cross-sectional schematic view of an embodiment of the apparatus. FIG. 63B shows a schematic cross-sectional view of an embodiment of the device. FIG. 63C shows a cross-sectional schematic view of an embodiment of the apparatus. FIG. 64A shows a cross-sectional schematic view of an embodiment of the apparatus. FIG. 64B shows a cross-sectional schematic view of an embodiment of the device. FIG. 64C shows a cross-sectional schematic view of an embodiment of the apparatus. FIG. 64D shows a cross-sectional schematic view of an embodiment of the device. FIG. 65A shows a cross-sectional schematic view of an embodiment of an infusion device connected to a fluid line. FIG. 65B shows a cross-sectional schematic view of an embodiment of an infusion device connected to a fluid line. FIG. 66A shows a schematic cross-sectional view of the order in which reservoirs are inserted into the device. FIG. 66B shows a schematic cross-sectional view of the order in which the reservoirs are inserted into the device. FIG. 66C shows a schematic cross-sectional view of the order in which the reservoirs are inserted into the device. FIG. 66D shows a schematic cross-sectional view of the order in which the reservoirs are inserted into the device. FIG. 67A shows a schematic diagram of an embodiment of a fluid delivery device. FIG. 67B shows a schematic diagram of an embodiment of a fluid delivery device. FIG. 67C shows a schematic diagram of an embodiment of a fluid delivery device. FIG. 67D shows a schematic diagram of an embodiment of a fluid delivery device. FIG. 67E shows a schematic diagram of an embodiment of a fluid delivery device. FIG. 67F shows a schematic diagram of an embodiment of a fluid delivery device. FIG. 68 is a schematic diagram of one of the portable pump embodiments of the device connected to the patient. FIG. 69A shows a schematic view of the bottom of the housing of the apparatus. FIG. 69B shows a schematic view of the bottom surface of the housing of the apparatus. FIG. 70 is a schematic diagram depicting various components available in an embodiment of a fluid delivery device. FIG. 70A is a schematic diagram depicting various components available in an embodiment of a fluid delivery device. FIG. 70B is a schematic diagram depicting various components available in an embodiment of a fluid delivery device. FIG. 70C is a schematic diagram depicting various components available in an embodiment of a fluid delivery device. FIG. 70D is a schematic diagram depicting various components available in an embodiment of a fluid delivery device. FIG. 71 schematically illustrates components that can be assembled to make a fluid delivery device, according to an embodiment of the device. FIG. 72 shows a side view of a fluid delivery device comprising an acoustic volumetric component. FIG. 73 shows a printed circuit board for acoustic volume measurement. FIG. 74 shows a perspective view of an embodiment of the device. FIG. 75 shows a perspective cross-sectional view of an embodiment of a fluid delivery device. FIG. 76 shows an exploded perspective view of an embodiment of a fluid delivery device. FIG. 77 shows an exploded view of components that can be assembled to make one embodiment of a fluid delivery device. FIG. 78 shows an exploded view of an embodiment of a fluid delivery device. FIG. 79 shows a base top view of one embodiment of a fluid delivery device. FIG. 80 shows the upper bottom surface of one embodiment of a fluid delivery device. FIG. 81A shows a sequence illustrating the process of clamping the reservoir 20 between the top and base. FIG. 81B shows a sequence illustrating the process of clamping the reservoir 20 between the top and base. FIG. 81C shows a sequence illustrating the process of sandwiching the reservoir 20 between the top and base. FIG. 82 shows an exploded top view of the device. FIG. 83 shows a bottom exploded view of one embodiment of the device showing the fluid path assembly, bottom housing and membrane, and adhesive. FIG. 84 shows a bottom view of the base showing the bottom of the fluid path assembly. FIG. 85A shows an exploded, partially exploded, and non-exploded view of an embodiment of the device. FIG. 85B shows an exploded, partially exploded, and non-exploded view of an embodiment of the device. FIG. 85C shows an exploded, partially exploded, and non-exploded view of an embodiment of the device. FIG. 85D shows an exploded, partially exploded, and non-exploded view of an embodiment of the device. FIG. 86A shows a schematic diagram of an infusion and sensor assembly with a connected infusion device and analyte sensor. FIG. 86B shows an exploded view of the injection and sensor assembly as shown in FIG. 86A with an introducer needle. FIG. 87A shows the sequence of embodiments of the injection and sensor assembly inserted into the device. FIG. 87B shows the sequence of embodiments of the injection and sensor assembly inserted into the device. FIG. 87C shows the sequence of embodiments of the injection and sensor assembly inserted into the device. FIG. 87D shows the sequence of embodiments of the injection and sensor assembly inserted into the device. FIG. 87E shows the sequence of embodiments of the injection and sensor assembly inserted into the device. FIG. 88A shows one embodiment of an insertion device in an order comprising an infusion and sensor assembly. FIG. 88B shows one embodiment of the insertion device in an order comprising an infusion and sensor assembly. FIG. 88C shows a partial cutaway view of the insertion device in FIGS. 88A-88B. FIG. 88D shows a partial cutaway view of the insertion device in FIGS. 88A-88B. FIG. 89A shows a front view of one embodiment of an insertion device for insertion of an injection and sensor assembly. FIG. 89B shows a rear view of the insertion device of FIG. 89A. FIG. 90 shows a perspective view of one embodiment of a cartridge for infusion and sensor assembly. FIG. 91A shows a perspective front and side view of an insertion device for insertion of an injection and sensor assembly. FIG. 91B shows a perspective front and side view of an insertion device for insertion of the injection and sensor assembly. FIG. 91C shows a perspective front and side view of an insertion device for insertion of the injection and sensor assembly. FIG. 92A schematically illustrates a temporal sequence for operation of one embodiment of an insertion device mechanism. FIG. 92B schematically illustrates the temporal sequence for operation of one embodiment of the inserter mechanism. FIG. 92C schematically illustrates the temporal sequence for operation of one embodiment of the inserter mechanism. FIG. 92D schematically illustrates the temporal sequence for operation of one embodiment of the inserter mechanism. FIG. 92E schematically illustrates the temporal sequence for operation of one embodiment of the inserter mechanism. FIG. 92F schematically illustrates the temporal sequence for operation of one embodiment of the inserter mechanism. FIG. 92G shows the insertion device mechanism in the closed position with pawls and cocking levers. FIG. 92H shows the insertion device mechanism in the open position with pawls and cocking levers. FIG. 93A shows a timeline for insertion of a cannula into the base of a fluid delivery device. FIG. 93B shows a timeline for insertion of a cannula into the base of the fluid delivery device. FIG. 93C shows a timeline for insertion of a cannula into the base of the fluid delivery device. FIG. 94A shows the time sequence for cannula insertion into the base, with simultaneous connection of the cannula to the fluid line. FIG. 94B shows the time sequence for cannula insertion into the base, with simultaneous connection of the cannula to the fluid line. FIG. 94C shows the time sequence for cannula insertion into the base with simultaneous connection of the cannula to the fluid line. FIG. 95 shows a top view of an adhesive patch for holding a fluid delivery device. FIG. 96 schematically shows a cross-sectional view of the fluid delivery device under the adhesive patch. FIG. 97 shows a perspective view of two overlapping adhesive patches for holding a fluid delivery device. FIG. 98 shows a top view of two semicircular adhesive patch portions. FIG. 99 shows a perspective view of two semicircular adhesive patch portions holding a fluid delivery device. FIG. 100 shows a perspective view of the semi-circular adhesive patch portion being removed by the patient. FIG. 101 shows a perspective view of a fluid delivery device held against a patient using a plurality of adhesive members and tethers. FIG. 102A shows a clamp for assembling the device. FIG. 102B shows the base of the fluid delivery device with a keyhole for inserting the clamp. FIG. 102C shows a cross-sectional view of the fluid delivery device assembled with a clamp. FIG. 103A shows a perspective view of a cam guide for use in assembling a fluid delivery device. FIG. 103B shows a top view of the cam guide of FIG. 103A. FIG. 103C shows a perspective view of a clamp pin for use in assembling a fluid delivery device. FIG. 103D shows an embodiment of a fluid delivery device assembled using a clamp pin and cam guide. FIG. 104 shows a cross-sectional view of a collapsible reservoir, according to one embodiment. FIG. 105 shows a perspective view of the reservoir of FIG. FIG. 106A illustrates a series of steps for securing a septum to a cap and creating a reservoir, according to one embodiment. FIG. 106B illustrates a series of steps for securing a septum to a cap and creating a reservoir, according to one embodiment. FIG. 106C illustrates a series of steps for securing a septum to a cap and creating a reservoir, according to one embodiment. FIG. 107 illustrates a reservoir filling station, according to one embodiment. FIG. 108A shows an embodiment of the reservoir filling station in both open (108A) and closed (108B) positions. FIG. 108B shows an embodiment of the reservoir filling station in both the open (108A) and closed (108B) positions. FIG. 109A shows a block diagram of an embodiment of a data acquisition and control scheme for an embodiment of a fluid delivery system. FIG. 109B shows a block diagram of an embodiment of a data acquisition and control scheme for an embodiment of a fluid delivery system. FIG. 110A shows a process diagram illustrating the operation of the fluid delivery device, according to one embodiment. FIG. 110B shows a process diagram illustrating the operation of the fluid delivery device, according to one embodiment. FIG. 111 shows a block diagram of a user interface and fluid delivery components in wireless communication with each other. FIG. 112 is a data flow diagram illustrating the use of an intermediate transceiver according to one embodiment. FIG. 113 shows a block diagram for an intermediate transceiver according to one embodiment. FIG. 114 shows a data flow diagram for a universal patient interface, according to one embodiment. FIG. 115 illustrates a non-disposable portion of a fluid delivery device in an unconnected state and a charger, according to one embodiment. FIG. 116 illustrates the non-disposable portion and charger of the fluid delivery device of FIG. FIG. 117 is a flow diagram depicting a process for measuring the volume of liquid delivered during a pump stroke, according to an embodiment of the present invention.

Claims (133)

(A) pumping fluid into an elastic variable volume dispensing chamber, wherein the dispensing chamber is in series with a normally present finite fluid impedance and outlet, wherein the impedance is a portion of the fluid Sufficient to cause expansion of the dispensing chamber while receiving the pumped fluid while flowing through the outlet;
(B) repeatedly measuring a parameter related to the volume of the dispensing chamber over time;
(C) controlling the pumping of the fluid based on repeated measurements of the parameter to produce a desired fluid flow through the outlet. The step of repeatedly measuring the parameter comprises:
Acoustically exciting a gas in an acoustically continuous region to produce an acoustic response in the region, wherein the region includes a sub-region coupled to the dispensing chamber; Causing a change in volume of the sub-region by a change in volume of the dispensing chamber; and
The method of claim 1, comprising characterizing the acoustic response.   The step of acoustically exciting the gas is performed at a single frequency only, and the step of characterizing the acoustic response includes an acoustic response when measured at a first location of the acoustically continuous region, and 3. The method of claim 2, comprising determining a phase relationship with a single frequency reference value, wherein the method further comprises calculating a volume change of the sub-region based on a temporal evolution of the phase relationship. The method described.   The method of claim 1, wherein the impedance is a passive impedance.   The method of claim 4, wherein the passive impedance comprises a conduit.   The method of claim 5, wherein the conduit comprises a coiled tube.   The method of claim 6, wherein the coiled tube includes at least two turning points.   The method of claim 5, wherein the conduit has a serpentine shape.   The method of claim 5, wherein the conduit has a length and an inner diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid.   The method of claim 9, wherein the inner diameter is sufficiently large to prevent blockage due to the flow of therapeutic agent flowing through the conduit.   The method of claim 10, wherein the conduit has a length greater than 2 cm.   Processes (a), (b), and (c) are performed by components in a patch-sized housing, the housing having a maximum dimension, and the conduit having a length that exceeds the maximum dimension. 6. The method of claim 5, comprising:   The method of claim 5, wherein the conduit includes a length selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid.   The method of claim 5, wherein the dispensing chamber has an inlet and the conduit has an inner diameter that is smaller than an inner diameter of the dispensing chamber inlet. The step of pumping fluid is
Providing an infusion line connectable to an upstream fluid source, wherein the infusion line is in fluid communication downstream with a pumping chamber, the pumping chamber having a pump outlet;
The method of claim 1, further comprising: actuating a force assembly to pressurize the pumping chamber and urge flow to the pump outlet while limiting back flow of fluid to the inlet.   16. The step of actuating the force assembly includes the step of limiting backflow and pressurizing the pumping chamber in a single mechanical action utilizing movement of the force assembly between work strokes. The method described.   The method of claim 16, wherein backflow is limited by a given mobility of the force actuating assembly and pressurizing the pumping chamber with greater mobility.   16. The method of claim 15, wherein actuating the force assembly includes restricting back flow to the fluid source by closing the infusion line.   16. The method of claim 15, further comprising preventing a reverse flow of fluid from the dispensing chamber to the pumping chamber using a passive valve mounted between the dispensing chamber and the pumping chamber. .   The method of claim 1, wherein pumping fluid further comprises allowing a portion of the fluid to return to a fluid source without flowing into the dispensing chamber. A patch-sized housing;
A pump included in the housing;
A dispensing assembly downstream of the pump in fluid communication with the pump, the dispensing assembly quantitatively determining an elastic dispensing chamber and a parameter related to the volume or time of the volume of the dispensing chamber. A sensor for measuring, the pump pulsating fluid to expand the elastic dispensing chamber every cycle, the chamber repeatedly delivering fluid to the outlet Assembly,
A control coupled to the sensor and the pump for controlling operation of the pump during normal flow conditions based on the measured parameter to achieve delivery of a fluid having a desired cumulative volume. A device for dispensing fluid, comprising: a control loop comprising a controller that determines a cumulative volume of fluid delivered through the outlet based on the measured parameter. An acoustic energy source that acoustically excites a gas in an acoustically continuous region and produces an acoustic response in the region, the region including a sub-region coupled to the dispensing chamber An acoustic energy source that causes a volume change of the sub-region due to a volume change of the dispensing chamber;
A processor and
The sensor is mounted at a first position in the acoustically continuous region and includes a first acoustic transducer for generating an electrical signal based on the acoustic response;
23. The processor of claim 21, wherein the processor is coupled to the first acoustic transducer and a reference value and implements a flow rate determination process to determine an amount related to a volume change of the sub-region based on the acoustic response. The device described.   The acoustic energy source excites the gas only at a single frequency, the electrical signal generated by the first acoustic transducer has a phase relationship to the reference value, and the flow determination process comprises: 23. The apparatus of claim 22, wherein an amount related to volume change of the sub-region is determined based on temporal evolution of the phase relationship.   24. The apparatus of claim 21, further comprising a finite fluid impedance coupled to the outlet, the finite fluid impedance being sufficient to allow such expansion of the elastic dispensing chamber.   25. The apparatus of claim 24, wherein the impedance is a passive impedance.   26. The apparatus of claim 25, wherein the passive impedance includes a conduit.   27. The apparatus of claim 26, wherein the conduit comprises a coiled tube.   28. The apparatus of claim 27, wherein the coiled tube includes at least two turning points.   27. The apparatus of claim 26, wherein the conduit has a serpentine shape.   27. The apparatus of claim 26, wherein the conduit has a length and an inner diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid.   32. The device of claim 30, wherein the inner diameter is sufficiently large to prevent blockage due to the flow of therapeutic agent flowing through the conduit.   32. The apparatus of claim 31, wherein the conduit has a length greater than 2 cm.   27. The apparatus of claim 26, wherein the housing has a maximum dimension and the conduit has a length that exceeds the maximum dimension.   27. The apparatus of claim 26, wherein the dispensing chamber has an inlet and the conduit has an inner diameter that is smaller than an inner diameter of the dispensing chamber inlet. The pump is
A pumping chamber having a connectable inlet for providing fluid communication with a fluid source and a pump outlet;
A force assembly adapted to provide a compression stroke to the pumping chamber, wherein the compression stroke restricts back flow of fluid from the pumping chamber to the inlet while the pump discharge from the pumping chamber. The apparatus of claim 21, wherein the apparatus biases fluid to the outlet.   When the force assembly is coupled to an inlet valve actuator and a pump actuator, the compression stroke is applied to the inlet when the pump actuator biases fluid from the pumping chamber to the pump outlet. 36. The device of claim 35, wherein the device operates an inlet valve coupled between the fluid source and the fluid source to close the valve.   37. The apparatus of claim 36, wherein the force assembly includes a plate coupled to the valve actuator, the pump actuator, and a motor for coordinated operation of the valve actuator and the pump actuator.   38. The apparatus of claim 37, wherein the motor includes a shape memory actuator.   40. The apparatus of claim 38, wherein the motor includes at least one pulley for folding the shape memory actuator to fit within a reusable portion.   24. The apparatus of claim 21, further comprising a shunt line in fluid communication with the pump outlet and a fluid source and capable of returning a portion of the fluid discharged by the pump back to the fluid source.   41. The apparatus of claim 40, wherein the fluid source includes a non-pressurized fluid reservoir.   An apparatus for dispensing fluid comprising a patch-sized housing enclosing a pressurized fluid source in series with a downstream flow-inhibiting distorted conduit. A sensor for measuring a parameter relating to the flow rate of fluid to the conduit;
43. The apparatus of claim 42, further comprising: a control loop for adjusting the fluid flow rate based on the measured parameter.   43. The apparatus of claim 42, wherein the source includes an operatively connected pump and provides pressurized fluid to the downstream flow-inhibiting distorted conduit. The pump is
A pumping chamber having an inlet connectable to provide fluid communication with a fluid source and a pump outlet;
A force assembly adapted to provide a compression stroke to the pumping chamber, wherein the compression stroke restricts backflow of fluid from the pumping chamber to the inlet while the pump discharge from the pumping chamber. 45. The device of claim 44, wherein the device biases fluid to the outlet.   When the force assembly is coupled to an inlet valve actuator and a pump actuator, the compression stroke is applied to the inlet when the pump actuator biases fluid from the pumping chamber to the pump outlet. 46. The apparatus of claim 45, wherein the apparatus operates an inlet valve coupled between the fluid source and the fluid source to close the valve.   47. The apparatus of claim 46, wherein the force assembly includes a plate coupled to the valve actuator, the pump actuator, and a motor for coordinated operation of the valve actuator and the pump actuator.   48. The apparatus of claim 47, wherein the motor includes a shape memory actuator.   49. The apparatus of claim 48, wherein the motor includes at least one pulley for folding the shape memory actuator to fit within a reusable portion.   45. The apparatus of claim 44, further comprising a shunt line in fluid communication with the pump outlet and a fluid source and capable of returning a portion of the fluid discharged by the pump back to the fluid source.   51. The apparatus of claim 50, wherein the fluid source includes a non-pressurized fluid reservoir. 45. The apparatus of claim 44, further comprising: a sensor for measuring a parameter related to fluid flow to the conduit; and a control loop for adjusting the fluid flow based on the measured parameter.   45. The apparatus of claim 44, wherein the source includes an operably coupled pump and provides pressurized fluid to the downstream flow hindrance distorted conduit.   43. The apparatus of claim 42, wherein the flow inhibition distorted conduit comprises a coiled tube.   55. The apparatus of claim 54, wherein the coiled tube includes at least two turning points.   43. The apparatus of claim 42, wherein the conduit has a serpentine shape.   43. The apparatus of claim 42, wherein the housing includes a disposable part having an integral fluid path with the flow-inhibiting distorted conduit.   43. The apparatus of claim 42, wherein the conduit is disposed within the housing.   43. The apparatus of claim 42, wherein the conduit has a length and an inner diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid.   43. The device of claim 42, wherein the inner diameter is sufficiently large to prevent obstruction due to the flow of therapeutic agent flowing through the conduit.   43. The apparatus of claim 42, wherein the conduit has a length greater than 2 cm.   43. The apparatus of claim 42, wherein the housing has a maximum dimension and the conduit has a length that exceeds the maximum dimension.   43. The apparatus of claim 42, further comprising a dispensing chamber comprising an inlet in fluid communication with the source and the conduit and receiving a fluid from the source and an outlet through which fluid is provided to the conduit.   64. The apparatus of claim 63, wherein the conduit has an inner diameter that is smaller than an inner diameter of the dispensing chamber inlet.   64. The apparatus of claim 63, wherein the dispensing chamber is an elastic variable volume dispensing chamber.   64. The apparatus of claim 63, wherein the conduit has an effective diameter that is smaller than an effective diameter of the inlet. A patch-sized housing;
A pump disposed in the housing and having a pump outlet;
Similarly, a dispensing chamber disposed in the housing and having a dispensing inlet and a dispensing outlet, wherein the dispensing inlet is connected to the pump outlet;
And a distorted conduit connected to the dispensing outlet and providing flow impedance. A sensor for measuring a parameter relating to the fluid flow to the conduit;
A control loop for adjusting the fluid flow rate based on the measured parameters;
68. The apparatus of claim 67, further comprising:   68. The apparatus of claim 67, further comprising an unpressurized reservoir disposed within the housing and operably coupled to provide fluid to the pump inlet.   68. The apparatus of claim 67, wherein the distorted conduit comprises a coiled tube.   72. The apparatus of claim 70, wherein the coiled tube includes at least two turning points.   68. The apparatus of claim 67, wherein the distorted conduit has a serpentine shape.   68. The apparatus of claim 67, wherein the housing includes a disposable portion having an integral fluid path with the distorted conduit.   68. The apparatus of claim 67, wherein the conduit is disposed within the housing.   68. The apparatus of claim 67, wherein the conduit has a length greater than 2 cm.   68. The apparatus of claim 67, wherein the housing has a maximum dimension and the conduit has a length that exceeds the maximum dimension.   68. The apparatus of claim 67, wherein the conduit includes an effective diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid.   68. The apparatus of claim 67, wherein the conduit has a length and an inner diameter selected to provide a predetermined impedance based on at least one of the viscosity and density of the fluid.   68. The apparatus of claim 67, wherein the dispensing chamber is an elastic variable volume dispensing chamber.   68. The apparatus of claim 67, wherein the dispensing chamber has an inlet and the conduit has an inner diameter that is smaller than an inner diameter of the dispensing chamber inlet. The pump is
A pumping chamber having a connectable inlet for providing fluid communication with a fluid source and a pump outlet;
A force assembly adapted to provide a compression stroke to the pumping chamber, wherein the compression stroke restricts back flow of fluid from the pumping chamber to the inlet while the pump discharge from the pumping chamber. 68. The device of claim 67, wherein the device biases fluid to the outlet.   When the force assembly is coupled to an inlet valve actuator and a pump actuator, the compression stroke is applied to the inlet when the pump actuator biases fluid from the pumping chamber to the pump outlet. 82. The apparatus of claim 81, wherein the apparatus operates an inlet valve connected between the fluid source and the fluid source to close the valve.   83. The apparatus of claim 82, wherein the force assembly includes a plate coupled to the valve actuator, the pump actuator, and a motor for coordinated operation of the valve actuator and the pump actuator.   The apparatus of claim 83, wherein the motor includes a shape memory actuator.   85. The apparatus of claim 84, wherein the motor includes at least one pulley for folding the shape memory actuator to fit within a reusable portion.   68. The apparatus of claim 67, further comprising a shunt line in fluid communication with the pump outlet and a fluid source and returning a portion of the fluid discharged by the pump to the fluid source.   90. The apparatus of claim 86, wherein the fluid source includes a non-pressurized fluid reservoir. During a volume change in a sub-region of an acoustically continuous region caused by fluid flow in a zone coupled to the volume of the subregion, acoustically excites a gas in the acoustically continuous region only at a single frequency; Producing an acoustic response; and
Determining a phase relationship between the acoustic response measured at a first location in the acoustically continuous region and a reference value of the single frequency;
Calculating a volume change of the sub-region based on temporal evolution of the phase relationship;
Inferring a measurement of fluid flow through the line based on the volume change of gas in the sub-region, and a method for measuring fluid flow delivered through the line.   90. The method of claim 88, further comprising measuring a reference value at a second location within the acoustically continuous region.   90. The method of claim 88, wherein the zone is connected to the volume of the sub-region through a membrane.   90. The method of claim 88, wherein the step of acoustically exciting a gas comprises driving a transducer.   90. The method of claim 88, wherein the step of acoustically exciting the gas comprises driving a speaker.   90. The method of claim 88, further comprising calibrating the phase relationship as a function of the volume of the sub-region.   90. The method of claim 88, wherein the acoustically continuous region has a volume of less than 200 microliters.   90. The method of claim 88, wherein the acoustically continuous region has a volume of less than 130 microliters.   90. The method of claim 88, wherein the acoustically continuous region has a volume of less than 10 microliters.   90. The method of claim 88, wherein calculating the volume change comprises determining such a change having a resolution better than 20 nanoliters.   90. The method of claim 88, wherein calculating the volume change comprises determining such a change having a resolution better than 15 nanoliters.   90. The method of claim 88, wherein calculating the volume change comprises determining such a change having a resolution better than 13 nanoliters.   90. The method of claim 88, wherein calculating the volume change comprises determining such a change having a resolution of at least 1/10000 of the volume of the acoustically continuous region.   90. The method of claim 88, wherein the single frequency is at or near the resonant frequency of the sub-region.   A calibration step is performed by acoustically exciting the region with a series of frequencies, the acoustic response measured at a first location in the acoustically continuous region, and the function as a function of the frequency. 90. The method of claim 88, further comprising determining a transfer function that characterizes a phase relationship of each of the series of frequencies with each reference value.   105. The method of claim 102, further comprising measuring a reference value for each of the series of frequencies at a second location within the acoustically continuous region.   105. The method of claim 102, further comprising detecting the presence of a bubble based on the transfer function.   105. The method of claim 104, further comprising entering an alarm condition based on detecting the presence of the bubble.   103. The method of claim 102, wherein calculating the volume change is repeated during the measurement phase, and the measurement phase is alternated with the calibration phase.   107. The method of claim 106, wherein the fluid is delivered every cycle and the calibration and measurement phase is coordinated with the cycle. During a volume change in a sub-region of an acoustically continuous region caused by fluid flow in a zone coupled to the volume of the subregion, acoustically excites a gas in the acoustically continuous region only at a single frequency; An acoustic energy source for producing an acoustic response;
A first acoustic transducer mounted at a first position in the acoustically continuous region and for generating an electrical signal based on the acoustic response, the first acoustic transducer comprising: The electrical signal has a first acoustic transducer having a phase relationship with respect to the reference value;
A processor coupled to the first acoustic transducer and the reference value, wherein an amount related to a volume change of the sub-region is obtained based on a temporal evolution of the phase relationship, and the gas in the sub-region A system for measuring fluid flow delivered through a line, comprising: a processor that implements a flow determination process to infer a measurement of fluid flow through the line based on volume change.   109. The system of claim 108, further comprising a second acoustic transducer mounted at a second location in the acoustically continuous region and generating an electrical signal that constitutes the reference value.   109. The system of claim 108, wherein the system has a power consumption of less than 500 joules per day. 109. A fluid delivery system utilizing the system for measuring fluid flow delivered through a line as recited in claim 108, wherein the fluid delivery system produces a flow of fluid delivered through the line comprising:
A pump coupled to the processor;
The power consumption by the processor does not substantially exceed the power consumption by the pump. The pump is
A pumping chamber having a connectable inlet for providing fluid communication with a fluid source and a pump outlet;
A force assembly adapted to provide a compression stroke to the pumping chamber, wherein the compression stroke restricts back flow of fluid from the pumping chamber to the inlet while the pump discharge from the pumping chamber. 112. The system of claim 111, wherein the system biases fluid to the outlet.   When the force assembly is coupled to an inlet valve actuator and a pump actuator, the compression stroke is applied to the inlet when the pump actuator biases fluid from the pumping chamber to the pump outlet. 119. The system of claim 112, wherein an inlet valve coupled between the fluid source and the fluid source is actuated to close the valve.   114. The system of claim 113, wherein the force assembly includes a plate coupled to the valve actuator, the pump actuator, and a motor for coordinated operation of the valve actuator and the pump actuator.   115. The system of claim 114, wherein the motor includes a shape memory actuator.   119. The system of claim 115, wherein the motor includes at least one pulley for folding the shape memory actuator to fit within a reusable portion.   109. The system of claim 108, further comprising a membrane connecting the zone to the volume of the sub-region.   109. The system of claim 108, wherein the acoustic energy source includes an acoustic transducer coupled to an electrical signal.   109. The system of claim 108, wherein the transducer is a speaker.   109. The system of claim 108, wherein the processor implements a calibration process for calibrating the phase relationship as a function of the volume of the sub-region.   109. The system of claim 108, wherein the acoustically continuous region has a volume of less than 200 microliters.   109. The system of claim 108, wherein the acoustically continuous region has a volume of 130 microliters or less.   109. The system of claim 108, wherein the acoustically continuous region has a volume of less than 10 microliters.   109. The system of claim 108, wherein the flow determination process determines an amount related to volume change that corresponds to a resolution better than 20 nanoliters.   109. The system of claim 108, wherein the flow determination process determines an amount related to volume change that corresponds to a resolution better than 15 nanoliters.   109. The system of claim 108, wherein the flow determination process determines an amount related to volume change that corresponds to a resolution better than 13 nanoliters.   109. The system of claim 108, wherein the flow determination process determines an amount related to a volume change that corresponds to a resolution of at least 1/10000 of the volume of the acoustically continuous region.   109. The system of claim 108, wherein the single frequency is at or near the resonant frequency of the sub-region. The acoustic source includes an acoustic radiation transducer coupled to the processor;
The processor implements a calibration process that causes the acoustic source to acoustically excite the region at a series of frequencies, and as part of such process, the processor includes an electrical signal of the first transducer; 109. The system of claim 108, wherein a transfer function is characterized that characterizes a phase relationship with a respective reference value of the series of frequencies as a function of the frequency.   129. The system of claim 129, wherein the processor implements a bubble detection process that detects the presence of bubbles based on the transfer function.   131. The system of claim 130, wherein the bubble detection process causes the system to enter an alarm state based on detecting the presence of the bubble.   132. The system of claim 131, wherein the flow determination process is repeated during the measurement phase, and the measurement phase is alternated with the calibration phase.   135. The system of claim 132, wherein the fluid is delivered on a cycle-by-cycle basis and the calibration and measurement phase is coordinated with the cycle.

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